CN114468990B

CN114468990B - Method and device for detecting components of living tissue and wearable equipment

Info

Publication number: CN114468990B
Application number: CN202110185765.7A
Authority: CN
Inventors: 徐可欣; 韩同帅; 孙迪; 刘雪玉
Original assignee: Xianyang Technology Co ltd
Current assignee: Xianyang Technology Co ltd
Priority date: 2021-02-11
Filing date: 2021-02-11
Publication date: 2023-03-24
Anticipated expiration: 2041-02-11
Also published as: EP4292531A1; WO2022170880A1; JP2024508717A; CN114468990A; KR20230147126A

Abstract

The embodiment of the disclosure provides a method and a device for detecting components of living tissues and wearable equipment. The method comprises the following steps: irradiating the detection area with at least one incident light with a preset wavelength, wherein the incident light passes through the detection area and then is emitted from at least one emitting position to form at least one beam of emergent light, and the incident positions of the incident light comprise at least two; acquiring light intensity values which are acquired by M photosensitive surfaces and correspond to each emergent light beam to acquire T output light intensities, wherein each output light intensity is acquired by processing according to the light intensity value of the emergent light acquired by one or more photosensitive surfaces, each photosensitive surface can acquire the light intensity value of the emergent light emitted from the emergent position in the preset anti-shaking range corresponding to the photosensitive surface, and T is more than or equal to 1 and less than or equal to M; the concentration of at least one measured tissue constituent is determined based on at least one output light intensity corresponding to at least one preset wavelength.

Description

Method and device for detecting components of living tissue and wearable equipment

Technical Field

The embodiment of the disclosure relates to the technical field of spectrum detection, in particular to a method and a device for detecting components of living tissues and wearable equipment.

Background

The body fluid of a human body contains various tissue components, such as blood sugar, fat, white blood cells and the like, and the concentration of each tissue component needs to be within the corresponding concentration range so as to ensure the healthy operation of the human body. However, for some individuals, the tissue components are easy to be unbalanced, i.e. the concentrations of the tissue components are not in the range, which leads to the body suffering from diseases, endangering health and even life, therefore, for such subjects, real-time detection of the tissue components is required.

Since the optical method has the characteristics of rapidness, no wound, multi-dimensional information and the like, the optical method is generally adopted for detecting the composition in the related art. Optical methods mainly include raman spectroscopy, polarization methods, optical coherence tomography, photoacoustic spectroscopy, mid-infrared spectroscopy, and near-infrared spectroscopy, etc., according to the detection principle.

In implementing the disclosed concept, the inventors found that there are at least the following problems in the related art: the detection accuracy by the related art is not high.

Disclosure of Invention

In view of the above, the disclosed embodiments provide a method, an apparatus and a wearable device for detecting living tissue components.

An aspect of an embodiment of the present disclosure provides a method of detecting a composition of a living tissue, the method including: irradiating a detection area with at least one incident light with a preset wavelength, wherein the incident light passes through the detection area and then is emitted from at least one emitting position to form at least one beam of emergent light, and the incident positions of the incident light comprise at least two; acquiring light intensity values which are acquired by M photosensitive surfaces and correspond to each emergent light beam to acquire T output light intensities, wherein each output light intensity is acquired by processing according to the light intensity value of the emergent light acquired by one or more photosensitive surfaces, each photosensitive surface can acquire the light intensity value of the emergent light emitted from the emergent position in the preset anti-shaking range corresponding to the photosensitive surface, and T is more than or equal to 1 and less than or equal to M; and determining the concentration of at least one measured tissue constituent according to at least one output light intensity corresponding to the at least one preset wavelength.

Another aspect of the disclosed embodiments provides an apparatus for detecting a composition of a living tissue, the apparatus including: the device comprises a light source module, a detection area, a light source module and a control module, wherein the light source module is used for irradiating the detection area with at least one incident light with a preset wavelength, the incident light passes through the detection area and then is emitted from at least one emitting position to form at least one beam of emitting light, and the incident positions of the incident light comprise at least two; the collecting module comprises M photosensitive surfaces, each photosensitive surface can collect the light intensity value of emergent light emitted from an emergent position in a preset anti-shaking range corresponding to the photosensitive surface, the collecting module is used for acquiring the light intensity value corresponding to each beam of emergent light collected by the M photosensitive surfaces to obtain T output light intensities, and each output light intensity is obtained by processing the light intensity value of the emergent light collected by one or more photosensitive surfaces; and the processing module is used for determining the concentration of at least one measured tissue component according to at least one output light intensity corresponding to the at least one preset wavelength.

According to another aspect of embodiments of the present disclosure, there is provided a wearable device including the apparatus for detecting a living tissue composition as described above.

According to the embodiment of the disclosure, the light intensity value of the emergent light emitted from the emergent position in the corresponding preset disturbance prevention range can be collected by the photosensitive surface, and the proportion of the area capable of stably receiving the emergent light in the photosensitive surface to the area of the photosensitive surface is improved by the photosensitive surface with the characteristics, so that the stability of receiving the emergent light is improved, the adverse effect of the change of the intensity distribution of the emergent light caused by shaking is reduced, and the detection precision is improved.

Drawings

The above and other objects, features and advantages of the present disclosure will become more apparent from the following description of embodiments of the present disclosure with reference to the accompanying drawings, in which:

FIG. 1 schematically illustrates a diagram of receiving emergent light with a relatively small-area photosurface in the presence of dither according to an embodiment of the disclosure;

FIG. 2 schematically illustrates a diagram of receiving emergent light with a larger area of a photosurface when dithering occurs according to an embodiment of the disclosure;

FIG. 3 schematically illustrates a flow chart of a method of detecting a composition of living tissue according to an embodiment of the present disclosure;

FIG. 4 is a schematic diagram illustrating a detection result obtained by a Monte Carlo simulation method according to an embodiment of the disclosure;

FIG. 5 schematically illustrates a schematic diagram of differential detection according to an embodiment of the disclosure;

FIG. 6 schematically illustrates a schematic view of an annular photosurface according to an embodiment of the disclosure;

FIG. 7 schematically illustrates a schematic view of a sector ring photosurface according to an embodiment of the disclosure;

FIG. 8 schematically illustrates a schematic view of a circular photosurface according to an embodiment of the disclosure;

FIG. 9 schematically illustrates a schematic view of a square photosurface in accordance with embodiments of the disclosure;

FIG. 10 is a schematic diagram illustrating a photosensitive surface obtained by masking an initial photosensitive surface according to an embodiment of the disclosure;

FIG. 11 schematically illustrates a block diagram of an apparatus for detecting a composition of living tissue according to an embodiment of the present disclosure;

FIG. 12 schematically illustrates a schematic diagram of diffuse detection according to an embodiment of the disclosure;

FIG. 13 schematically illustrates a schematic diagram of an electrical connection of anodes to different photosurfaces in accordance with an embodiment of the disclosure;

FIG. 14 schematically illustrates a schematic view of a contoured glazing in the form of a glove according to an embodiment of the present disclosure;

FIG. 15 schematically illustrates a schematic view of a third dimensional gloss surface in the form of another glove according to an embodiment of the present disclosure;

FIG. 16 schematically illustrates a schematic view of a solid photosurface in the form of a bracelet according to an embodiment of the disclosure;

FIG. 17 schematically illustrates a schematic view of another solid photosurface in the form of a bracelet according to an embodiment of the disclosure;

FIG. 18 schematically illustrates a schematic view of a stereoscopic optical surface for arm detection, according to an embodiment of the disclosure;

FIG. 19 is a schematic diagram illustrating a convex lens and a circular photosurface in combination for achieving light reception in accordance with an embodiment of the disclosure;

FIG. 20 is a schematic diagram illustrating a ring lens and a ring-shaped photosensitive surface combined to achieve light reception in accordance with an embodiment of the disclosure;

FIG. 21 is a schematic diagram illustrating an arrangement of a plurality of convex lenses to form a ring lens and a ring-shaped photosensitive surface to achieve light receiving in combination according to an embodiment of the disclosure;

FIG. 22 is a schematic diagram illustrating a plurality of convex lenses arranged to form a ring lens and a circular photosensitive surface in combination to achieve light receiving according to an embodiment of the disclosure;

FIG. 23 is a schematic diagram illustrating a circular photosurface and filter film combination for achieving light reception in accordance with an embodiment of the disclosure;

FIG. 24 is a schematic diagram illustrating a fan-ring photosurface and filter film combination for achieving light reception according to an embodiment of the disclosure;

FIG. 25 schematically illustrates a schematic view of a first sleeve disposed on a test probe according to an embodiment of the disclosure;

FIG. 26 schematically illustrates a schematic view of a first sleeve externally locating a second sleeve within a target area in accordance with an embodiment of the disclosure;

FIG. 27 schematically illustrates a diagram of a photosurface receiving outgoing light without being filled with an index match according to an embodiment of the disclosure;

FIG. 28 schematically illustrates a diagram of a photosurface receiving outgoing light with an index match filled in accordance with an embodiment of the disclosure;

FIG. 29 schematically illustrates another diagram of a photosurface receiving outgoing light with an index match filled in accordance with an embodiment of the disclosure;

FIG. 30 schematically illustrates a schematic diagram of the peripheral reception of a circular incident light and a ring-shaped incident light incident on a ring-shaped photosurface in accordance with an embodiment of the disclosure;

fig. 31 is a schematic diagram illustrating the peripheral reception of a circular incident light and a ring-shaped incident light incident on the first set of photosurfaces in accordance with an embodiment of the disclosure;

FIG. 32 is a schematic diagram illustrating the peripheral reception of circular incident light and annular incident light incident on the second set of photosurfaces in accordance with an embodiment of the disclosure;

FIG. 33 is a schematic diagram illustrating peripheral reception of two annular incident lights into the interior of a circular photosurface according to an embodiment of the disclosure;

FIG. 34 schematically illustrates a schematic view of two annular incident light beams peripherally incident and received internally by a third set of photosurfaces, in accordance with an embodiment of the disclosure;

FIG. 35 schematically illustrates a schematic diagram of nested reception according to an embodiment of the present disclosure;

FIG. 36 schematically illustrates a schematic diagram of another nested receive, according to an embodiment of the disclosure;

FIG. 37 schematically illustrates a schematic diagram of yet another nested receive, according to an embodiment of the present disclosure;

figure 38 schematically illustrates a schematic diagram of a wearable device according to an embodiment of the present disclosure;

figure 39 schematically illustrates a schematic diagram of an assembly process of a wearable device according to an embodiment of the present disclosure;

fig. 40 schematically shows a schematic diagram of keeping an average optical path of emergent light received by a detection probe within a preset optical path range during skin jitter if a wearable device is consistent with a skin jitter rule according to an embodiment of the present disclosure; and

fig. 41 schematically shows a schematic diagram of an average optical path of outgoing light received by a detection probe remaining within a preset optical path range during skin shaking if a wearable device causes a movement amplitude of skin at a detection area to be less than or equal to a movement amplitude threshold value, according to an embodiment of the disclosure.

Detailed Description

Hereinafter, embodiments of the present disclosure will be described with reference to the accompanying drawings. It should be understood that the description is illustrative only and is not intended to limit the scope of the present disclosure. In the following detailed description, for purposes of explanation, numerous specific details are set forth in order to provide a thorough understanding of the embodiments of the disclosure. It may be evident, however, that one or more embodiments may be practiced without these specific details. Moreover, in the following description, descriptions of well-known structures and techniques are omitted so as to not unnecessarily obscure the concepts of the present disclosure.

The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the disclosure. The terms "comprises," "comprising," and the like, as used herein, specify the presence of stated features, steps, operations, and/or components, but do not preclude the presence or addition of one or more other features, steps, operations, or components.

All terms (including technical and scientific terms) used herein have the same meaning as commonly understood by one of ordinary skill in the art unless otherwise defined. It is noted that the terms used herein should be interpreted as having a meaning that is consistent with the context of this specification and should not be interpreted in an idealized or overly formal sense.

Where a convention analogous to "at least one of A, B, and C, etc." is used, in general such a construction is intended in the sense one having skill in the art would understand the convention (e.g., "a system having at least one of A, B, and C" would include but not be limited to systems that have A alone, B alone, C alone, A and B together, A and C together, B and C together, and/or A, B, and C together, etc.). Where a convention analogous to "at least one of A, B, or C, etc." is used, in general such a construction is intended in the sense one having skill in the art would understand the convention (e.g., "a system having at least one of A, B, or C" would include but not be limited to systems that have A alone, B alone, C alone, A and B together, A and C together, B and C together, and/or A, B, and C together, etc.).

The research of detecting the components of the living tissue based on the optical method has been developed for nearly fifty years, and although a great deal of research enthusiasm has been put into the field by scientific research institutes and companies, the detected tissue components are generally weakly absorbed, and the variation range of the concentration of the detected tissue components of the detected living body is generally not large, so the detected tissue component signals are generally weak, and the detected tissue component signals are easily interfered by the change of the detection conditions and the like, and the weak detected tissue component signals are easily submerged by the interference, so that a scheme for realizing reliable tissue component detection has not been developed yet. Therefore, the detection of the components of living tissues is a world problem to be solved urgently. The tissue components may include blood glucose, fat, leukocytes, etc. The measured tissue constituent signal represents a change in output light intensity caused by a change in concentration of the measured tissue constituent. The detection condition may be understood as a condition that affects the transmission path of light. The detection conditions may include controllable detection conditions and uncontrollable detection conditions. The controllable detection condition refers to a detection condition which can be kept within a preset variation range (namely, kept unchanged or basically kept unchanged) by adopting an effective control method in each tissue component detection process, wherein the effective control method can be realized by matching with hardware design. An uncontrollable detection condition refers to a detection condition having characteristics that are difficult to predict and uncontrollable. The controllable detection conditions may include temperature, pressure, detection area, detection posture, and the like. The uncontrollable detection conditions may include physiological background variations, detection device drift, and the like.

In implementing the presently disclosed concept, the inventors have found that the main reason why the detection accuracy is not high with the related art is.

The inventors have found that the detection results obtained are different if the intensity distribution of only the spot of light irradiated by the incident light onto the detection area is changed without changing other conditions. If the light-sensitive surface is arranged close to the blood vessel to obtain a detection result, compared with the detection result obtained by arranging the same light-sensitive surface far away from the blood vessel under the condition that other conditions are not changed, the detection result obtained by arranging far away from the blood vessel is better than the detection result obtained by arranging close to the blood vessel. The detection result can be represented by the relative variation of the light intensity value of the emergent light received by the photosensitive surface or the standard deviation of the light intensity value, the smaller the relative variation of the light intensity value is, the more excellent the detection result is, the smaller the standard deviation of the light intensity value is, and the more excellent the detection result is. When different reasons of detection results are researched, the fact that the randomness of light source irradiation can be represented by changing the intensity distribution of light spots irradiated to a detection area by incident light, the strength of pulse beat can be represented by the distance between the light spots and blood vessels, and the randomness of the light source irradiation and the pulse beat are sources of jitter. Thus, it was found that one of the causes of the low detection accuracy is jitter.

On the basis of the study on jitter, it was found that jitter can be divided into internal and external sources depending on the source causing it. The internal source may include a physiological background variation in addition to the pulse beat. External sources may include, in addition to randomness in the illumination of the light source, uncertainty in the transmission of the incident light itself. The randomness of the illumination of the light source may be reflected by the intensity distribution of the spot of light illuminated by the incident light onto the detection area. And the jitter caused by an internal source or an external source affects the transmission path of light in the tissue, so that the intensity distribution of emergent light on the detection area is affected.

In order to solve the problem of low detection accuracy caused by jitter, the inventors found that a scheme of collecting the light intensity value of the emergent light by using a photosensitive surface with a large area (i.e., a large-area photosensitive surface) can be adopted to effectively suppress the adverse effect of jitter on the detection result. The large-area light-sensitive surface can effectively inhibit adverse effects caused by shaking, and the large-area light-sensitive surface can be understood as the area of the light-sensitive surface, so that the light-sensitive surface can acquire the light intensity value of emergent light emitted from the emergent position within the preset shake prevention range. The large-area light-sensitive surface is continuous in area, and is made of a photosensitive material, which is different from single-point optical fiber receiving and multiple single optical fiber combined receiving. The following will specifically explain why the scheme of collecting the output light intensity of the emergent light by using the large-area photosensitive surface can effectively suppress the adverse effect of jitter on the detection result.

Because the large-area photosurface can improve the proportion of the area of the photosurface, which can stably receive the emergent light, in the photosurface, in the area of the photosurface, the stability of receiving the emergent light can be improved, and then the adverse effect of the change of the intensity distribution of the emergent light caused by jitter can be reduced, thereby improving the detection precision. The stability can be represented by the relative variation of the light intensity value of the emergent light received by the photosensitive surface or the standard deviation of the light intensity value, the smaller the relative variation of the light intensity value is, the higher the stability is, the smaller the standard deviation of the light intensity value is, and the higher the stability is.

Schematically, the shaking caused by the pulse beat will be described as an example. The pulse beat can be reflected by the state of the blood vessels. Fig. 1 schematically illustrates a schematic diagram of receiving emergent light with a small-area photosensitive surface in the presence of jitter according to an embodiment of the disclosure. Fig. 2 schematically illustrates a schematic diagram of receiving emergent light by using a large-area photosensitive surface when dithering occurs according to an embodiment of the disclosure. The jitter occurred in fig. 1 and fig. 2 is the same. The area of the sensing surface a in fig. 1 is smaller than the area of the sensing surface B in fig. 2. The photosensitive surface A and the photosensitive surface B are both square photosensitive surfaces. In fig. 1 and 2, a vascular state 1 indicates a vasoconstriction state, a vascular state 2 indicates a vasodilation state, a skin state 1 indicates a skin state corresponding to the vascular state 1, and a skin state 2 indicates a skin state corresponding to the vascular state 2. The skin state 1 to the skin state 2 represent shaking.

In the case where the same shake occurs, the detection results obtained with the photosensitive surfaces of different areas are compared. The detection result is represented by the relative variation of the light intensity value of the emergent light received by the photosensitive surface in a preset time period or the standard deviation of the light intensity value. Wherein the relative change of the light intensity value can be determined by: calculating the difference value between the maximum light intensity value and the minimum light intensity value in a preset time period, calculating the average value of the emergent values in the preset time period, calculating the ratio of the difference value to the average value, and taking the ratio as the relative variation of the light intensity values. The preset time period may be one pulsation cycle.

The detection result also shows that whether the relative variation of the light intensity value of the emergent light received by the photosensitive surface is adopted to represent the detection result or the standard deviation of the light intensity value of the emergent light received by the photosensitive surface is adopted to represent the detection result, the detection result obtained by adopting the photosensitive surface B is superior to the detection result obtained by adopting the photosensitive surface A.

Since the area of the photosensitive surface B is larger than that of the photosensitive surface a, it can be shown that the large-area photosensitive surface can improve the stability of receiving the outgoing light, and further can reduce the adverse effect of the change in intensity distribution of the outgoing light caused by jitter, thereby improving the detection accuracy.

In addition, because the output light intensity of the emergent light is weak, the output light intensity change caused by the concentration change of the detected tissue components is also weak, and the efficiency of the emergent light received by the emergent light receiving mode adopted in the related technology is low, the signal-to-noise ratio of the received output light intensity is low, and the detection precision is low. The large-area light-sensing surface can improve the signal-to-noise ratio of output light intensity, and further improve detection precision. The large-area light-sensitive surface can receive emergent light in a large range, so that the efficiency of receiving the emergent light is improved, the signal-to-noise ratio of output light intensity can be improved, and the detection precision is improved.

It should be noted that the large-area photosensitive surface according to the embodiment of the disclosure can achieve high stability and efficiency of receiving and emitting light under the condition that the distance from the surface of the detection area is small, that is, under the condition that the large-area photosensitive surface is close to the surface of the detection area. This is not possible with single-point fiber reception and multiple single-fiber joint reception because, for one thing, it is limited by the numerical aperture constraints of the fibers; secondly, it is limited by the state change of the optical fiber. The state change of the optical fiber is easily influenced by the environment, and the change of the optical fiber has great influence on the stability of receiving emergent light.

It should also be noted that a large area photosurface can be used, typically to improve the signal-to-noise ratio of the output light intensity. In other words, the large-area photosurface generally functions to improve the signal-to-noise ratio of the output light intensity, unlike the large-area photosurface that mainly functions in the disclosed embodiment, which mainly functions to effectively suppress jitter. The following description will be given with reference to specific examples.

FIG. 3 schematically illustrates a flow chart of a method of detecting a composition of living tissue according to an embodiment of the disclosure.

As shown in fig. 3, the method includes operations S310 to S330.

In operation S310, the detection area is irradiated with at least one incident light with a preset wavelength, wherein the incident light passes through the detection area and then exits from at least one exit position to form at least one outgoing light beam, and the incident positions of the incident light include at least two.

According to the embodiment of the present disclosure, since different detection portions have different skin characteristics, which may include a smoothness degree, a presence or absence of hair, a flat state, a skin thickness, a softness degree, and the like, it is necessary to select an appropriate detection portion according to actual conditions, such as a structure of a detection probe. The detection site may include at least one of a finger, a palm, an arm, a forehead, and an earlobe. The detection area may be an area on the detection site.

According to an embodiment of the present disclosure, the preset wavelength may be a wavelength sensitive to a measured tissue component. The band to which the preset wavelength belongs may include an ultraviolet band, a visible light band, a near-infrared band, a mid-infrared band, or a far-infrared band. Illustratively, if the tissue to be measured is blood glucose, the predetermined wavelength may be a wavelength sensitive to blood glucose, and specifically 1550nm or 1609nm. The incident light may be collimated light or non-collimated light. The incident positions of the incident light may include at least two.

In operation S320, light intensity values corresponding to each outgoing light beam collected by the M photosensitive surfaces are obtained, and T output light intensities are obtained, where each output light intensity is obtained by processing the light intensity values of the outgoing light collected by one or more photosensitive surfaces, each photosensitive surface can collect the light intensity value of the outgoing light emitted from an outgoing position within a preset anti-shake range corresponding to the photosensitive surface, and T is greater than or equal to 1 and less than or equal to M.

According to the embodiment of the disclosure, in order to improve the detection accuracy, it is required to ensure that each photosensitive surface can collect the light intensity value of the emergent light emitted from the emergent position within the preset anti-shake range corresponding to the photosensitive surface as much as possible, which requires that the area of the photosensitive surface is as large as possible. Each photosensitive surface has a corresponding preset anti-shaking range, and the preset anti-shaking ranges of different photosensitive surfaces are the same or different. The greater the area of the photosensitive surface employed, the better the effect of suppressing the shake, will be described below in connection with an example from three points of view. The area of the light sensing surface A is preset to be smaller than that of the light sensing surface B. The photosensitive surface A and the photosensitive surface B are both square photosensitive surfaces.

First, jitter caused by pulse beat is suppressed. The light-sensing surface A and the light-sensing surface B are respectively arranged at the same position on the detection area, and the position is close to a blood vessel. Under the condition of the same other conditions, the detection results obtained by adopting the photosensitive surface A and the photosensitive surface B are compared, wherein the detection results are represented by the relative variation of the light intensity values of the emergent light received by the photosensitive surfaces in a pulse period or the standard deviation of the light intensity values. The calculation of the relative variation of the light intensity values is as described above, and is not described herein again. The relative variation of the light intensity value of the emergent light received by the photosensitive surface B is smaller than that of the emergent light received by the photosensitive surface A, and the standard deviation of the light intensity value of the emergent light received by the photosensitive surface B is smaller than that of the emergent light received by the photosensitive surface A. Therefore, no matter the relative variation of the light intensity value of the emergent light received by the photosensitive surface is adopted to represent the detection result, or the standard deviation of the light intensity value of the emergent light received by the photosensitive surface is adopted to represent the detection result, the detection result obtained by adopting the photosensitive surface B is superior to the detection result obtained by adopting the photosensitive surface A.

Since the detection result obtained by using the photosensitive surface B is better than the detection result obtained by using the photosensitive surface a, and the area of the photosensitive surface B is larger than that of the photosensitive surface a, it can be said that the larger the area of the photosensitive surface is, the better the effect of suppressing the jitter caused by the pulse beat is.

Secondly, jitter caused by variation in intensity distribution of a spot irradiated to the detection area by incident light is suppressed. With other conditions unchanged, only the intensity distribution of the spot of incident light impinging on the detection area is changed. And comparing the detection results obtained by adopting the photosensitive surface A and the photosensitive surface B, wherein the detection results are represented by the relative variation of the light intensity values of the received emergent light of the photosensitive surfaces in a preset time period or the standard deviation of the light intensity values. The calculation of the relative variation of the light intensity values is as described above and will not be described herein. The change amount of the light intensity value of the emergent light received by the photosensitive surface B is smaller than that of the emergent light received by the photosensitive surface A, and the standard deviation of the light intensity value of the emergent light received by the photosensitive surface B is smaller than that of the emergent light received by the photosensitive surface A. Therefore, no matter the relative variation of the light intensity value of the emergent light received by the photosensitive surface is adopted to represent the detection result, or the standard deviation of the light intensity value of the emergent light received by the photosensitive surface is adopted to represent the detection result, the detection result obtained by adopting the photosensitive surface B is superior to the detection result obtained by adopting the photosensitive surface A.

Since the detection result obtained by using the photosensitive surface B is superior to the detection result obtained by using the photosensitive surface a, and the area of the photosensitive surface B is larger than that of the photosensitive surface a, it can be said that the larger the area of the photosensitive surface is, the better the effect of suppressing jitter caused by the variation in the intensity distribution of the light spot irradiated to the detection region by the incident light is.

Thirdly, suppressing the uncertainty caused by the transmission of the incident light itselfJitter of (2). A monte carlo simulation method is used. With the number of photons being 10 ¹⁵ The light sensing surface A and the light sensing surface B are respectively arranged at the position 2.4mm away from the center of the incident light, and the simulation times are 22 times. And comparing detection results obtained by adopting the photosensitive surface A and the photosensitive surface B, wherein the detection results are represented by standard deviation of the number of emitted photons per unit area, and the smaller the standard deviation of the number of emitted photons per unit area is, the better the inhibition effect is. Fig. 4 is a schematic diagram illustrating a detection result obtained by a monte carlo simulation method according to an embodiment of the disclosure. It is found that the standard deviation of the number of emitted photons per unit area corresponding to the light-sensing surface B is smaller than the standard deviation of the number of emitted photons per unit area corresponding to the light-sensing surface a. That is, the detection result obtained by using the photosensitive surface B is superior to that obtained by using the photosensitive surface a.

Since the detection result obtained by using the photosensitive surface B is superior to the detection result obtained by using the photosensitive surface a, and the area of the photosensitive surface B is larger than that of the photosensitive surface a, it can be said that the larger the area of the photosensitive surface is, the better the effect of suppressing jitter caused by uncertainty in transmission of incident light itself is.

By the above three examples, it is explained that the larger the area of the light-sensing surface is, the better the effect of suppressing the adverse effect of the shake on the detection result is.

According to the embodiment of the disclosure, each photosensitive surface may be an annular photosensitive surface or a non-annular photosensitive surface, where the non-annular photosensitive surface may include a sector-ring photosensitive surface, a circular photosensitive surface, a sector-shaped photosensitive surface, an oval photosensitive surface, or a polygonal photosensitive surface. The polygonal photosensitive surface may include a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

According to the embodiment of the disclosure, each photosensitive surface in the M photosensitive surfaces can be used alone, partially or totally in combination, and the combination means that one output light intensity is output. In the embodiments of the present disclosure, the photosensitive surface for outputting an output light intensity is referred to as a similar photosensitive surface, and the similar photosensitive surface may include one or more photosensitive surfaces. The condition that different photosensitive surfaces are used in combination may be that the average optical path of the outgoing light received by each photosensitive surface is within the average optical path range. The average optical path range may be a range composed of greater than or equal to the first average optical path threshold and less than or equal to the second average optical path threshold. The first average optical path threshold and the second average optical path threshold may be determined according to an optical path average value and an optical path variation amplitude. The average value of the optical paths is an average value calculated according to the average optical paths of emergent light received by all photosensitive positions of the same type of photosensitive surfaces. For example, if the average value of the optical path is a and the amplitude of the optical path variation is ± 30%, the first average optical path threshold may be 0.7a and the second average optical path threshold may be 1.3a.

The average optical length is explained as follows. The transmission path of light in tissue can be represented by an optical path length, which is used to represent the total distance light travels in tissue, and a penetration depth, which is used to represent the maximum longitudinal distance light can reach in tissue. For a determined source-probe distance, the average path length is used to represent the average of the path length of light in the tissue. The probability distribution function of the optical path length can be understood as a function of the source probe distance, which represents the radial distance between the center of the incident light and the center of the photosurface, and the tissue optical parameters. Accordingly, in mathematical terms, the mean optical path length is understood to be a function of the source-probe distance and the tissue optical parameters, which may include absorption coefficients, scattering coefficients and anisotropy factors. Factors that affect the average optical path may include absorption coefficients, scattering coefficients, anisotropy factors, and source-probe distances.

According to embodiments of the present disclosure, the same type of photosurface may be an annular photosurface or a non-annular photosurface. The similar photosensitive surfaces are annular photosensitive surfaces, and may include that the similar photosensitive surfaces are independent annular photosensitive surfaces in the case that the similar photosensitive surfaces include one photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is an annular photosensitive surface formed by combining the plurality of photosensitive surfaces. The same type of photosensitive surface is a non-annular photosensitive surface, which may include that the same type of photosensitive surface is an independent non-annular photosensitive surface in the case that the same type of photosensitive surface includes one photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed according to a combination of the plurality of photosensitive surfaces.

In operation S330, a concentration of at least one measured tissue constituent is determined according to at least one output light intensity corresponding to at least one preset wavelength.

According to the embodiment of the disclosure, after obtaining at least one output light intensity corresponding to at least one preset wavelength, for each measured tissue component, an interference suppression method may be adopted to process the at least one output light intensity corresponding to the at least one preset wavelength to determine the concentration of the measured tissue component. The interference suppression method may include a differential detection method. The differential detection method may include a time differential detection method, a position differential detection method, or a wavelength differential detection method. Alternatively, the at least one output intensity may be processed using a non-differential detection method to determine the concentration of the measured tissue constituent.

According to the technical scheme of this disclosed embodiment, the light intensity value of the emergent light that the emergent position that the sensitive surface can gather in the preset disturbance range of preventing that corresponds was emergent, because the sensitive surface that has above-mentioned characteristic has improved the area that can stably receive the emergent light in the sensitive surface and has accounted for the proportion of the area of this sensitive surface, consequently, has improved the stability of receiving the emergent light, and then has reduced the adverse effect of the change of the intensity distribution of the emergent light that leads to by the shake to detection accuracy has been improved.

According to the embodiment of the disclosure, the proportion of the average optical path of the emergent light received by each photosensitive surface in the target tissue layer to the total optical path is greater than or equal to a proportion threshold value, wherein the total optical path is the total distance transmitted by the emergent light in the detection area.

According to embodiments of the present disclosure, the tissue model of the living subject being examined is generally a layered structure, i.e., may be divided into one or more layers. The information of the detected tissue components carried by different tissue layers is different, and in order to improve the detection precision, the transmission path of the emergent light needs to be made as much as possible mainly through the tissue layer carrying the detected tissue components and having richer information. The target tissue layer may be understood as a relatively informative tissue layer carrying the measured tissue composition, or a tissue layer which is the main source of the measured tissue composition. The following description will be given taking the living body to be tested as a human body and the tissue to be tested as blood sugar.

The skin tissue model of a human body is understood to be a three-layer model, namely, from the outside to the inside, the epidermis layer, the dermis layer and the subcutaneous fat layer. The epidermis layer contains a small amount of interstitial fluid and does not contain plasma and lymph fluid. The dermis contains a large amount of interstitial fluid and, due to the presence of abundant capillaries, also contains a large amount of plasma and a small amount of lymph fluid. The subcutaneous fat layer contains a small amount of cellular fluid, and, due to the presence of blood vessels such as veins and arteries, contains a large amount of plasma and a small amount of lymph fluid. It follows that different tissue layers carry different information about the measured tissue composition.

The epidermis layer is not a suitable source of glycemic information, since it contains small amounts of interstitial fluid. Although the subcutaneous fat layer contains a large amount of plasma and a relatively small amount of interstitial fluid, the subcutaneous fat layer is also not a suitable source of blood glucose information due to the limited penetration depth of incident light. The dermis can be the main source of blood glucose information because it contains abundant capillaries and large amounts of tissue fluid and is easily accessible to incident light. Accordingly, the target tissue layer may be a dermal layer.

According to embodiments of the present disclosure, an average optical path of the emerging light in each tissue layer may be determined according to the optical path and the penetration depth.

In order to ensure that the transmission path of the emergent light is mainly the emergent light passing through the target tissue layer as much as possible, the proportion of the average optical path of the emergent light received by each photosensitive surface in the target tissue layer to the total optical path is required to be larger than or equal to a proportion threshold, wherein the total optical path can be the total distance of the emergent light transmitted in the detection area, namely the total distance of the path of the incident light transmitted from the incident light to the emergent position in the detection area. Wherein the proportional threshold is related to a source-detector distance between a center of the photosurface and a center of the incident light and the tissue optical parameters.

It should be noted that, since the embodiment of the present disclosure defines a ratio of an average optical path of the emergent light received by the light sensing surface in the target tissue layer to a total optical path, an area of the light sensing surface of the embodiment of the present disclosure cannot be too large, which is a large area within an area range.

According to an embodiment of the present disclosure, the method may further include the following operations.

And determining the total area of the same type of photosensitive surfaces according to the tissue structure characteristics in the detection area, wherein the same type of photosensitive surfaces comprise one or more photosensitive surfaces and are used for outputting an output light intensity.

According to the embodiment of the disclosure, the total area of the same kind of photosensitive surfaces can be determined according to the tissue structure characteristics in the detection area. The tissue structure feature is understood to be a structure feature of the detection region.

For example, if the detection region is a region where three blood vessels intersect, if the same type of photosensitive surfaces are disposed in the region where the three blood vessels intersect, the total area of the same type of photosensitive surfaces is limited by the area of the region where the three blood vessels intersect, that is, the total area of the same type of photosensitive surfaces needs to be determined according to the area of the region where the three blood vessels intersect.

If the same type of photosensitive surface is arranged in the region where the finger is located, the total area of the same type of photosensitive surface is limited by the area of the region where the finger is located, that is, the total area of the same type of photosensitive surface needs to be determined according to the area of the region where the finger is located.

It should be noted that, since the area of the photosensitive surface in the embodiment of the present disclosure may be determined according to the tissue structure characteristics, and the area generally determined according to the tissue structure characteristics cannot be too large, the area of the photosensitive surface in the embodiment of the present disclosure cannot be too large, which is a large area within the area range.

According to an embodiment of the disclosure, a ratio of an area of each photosensitive surface to a perimeter of the photosensitive surface is greater than or equal to a ratio threshold.

According to the embodiment of the disclosure, in order to reduce the influence of the uncertainty of incident light transmission, the randomness of the light source, the physiological background variation, and the jitter caused by pulse beat on the distribution of the emergent light on the detection area, the ratio of the area of the photosensitive surface to the circumference of the photosensitive surface may be made as large as possible, that is, it is necessary to ensure that the ratio is greater than or equal to the ratio threshold.

For convenience of explanation, the photosensitive surface is hereinafter divided into two parts, i.e., an edge part and a non-edge part (or an inner part). Usually, the main influence of the jitter is the emergent light collected by the edge part, and the influence on the non-edge part is small, namely, the non-edge part can collect the emergent light more stably. It is understood that, in the presence of jitter, the intensity distribution of the outgoing light in the detection area changes slightly, so that the light intensity value of the outgoing light received by the edge portion changes greatly along with the change of the intensity distribution of the outgoing light, and most of the outgoing light at the non-edge portion can be stably collected by the photosensitive surface, so that the light intensity value of the outgoing light received by the non-edge portion can be kept relatively stable. Therefore, in order to effectively suppress the adverse effect of the jitter on the detection result, the ratio of the area corresponding to the non-edge portion to the area of the light-sensing surface can be made as large as possible, and the effect of reducing the adverse effect is better when the ratio is larger. Wherein the edge portion may be characterized by a perimeter of the photosurface and the non-edge portion may be characterized by an area of the photosurface. This makes it possible to maximize the ratio of the area of the light-sensing surface to the perimeter of the light-sensing surface.

For example, if the photosensitive surface 1 is a circular photosensitive surface and the photosensitive surface 2 is a square photosensitive surface, in the case of the same perimeter, since the area of the photosensitive surface 1 is larger than the area of the photosensitive surface 2, the ratio of the area of the photosensitive surface 1 to the perimeter is larger than the ratio of the area of the photosensitive surface 2 to the perimeter, and thus the adverse effect of the photosensitive surface 1 is better than that of the photosensitive surface 2.

It should be noted that the description is made on the condition that the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold value when the area of the photosensitive surface is satisfied and is greater than or equal to the area threshold value. For most shapes of photosurfaces, it is also practical to limit the size of the area of the photosurface, typically if the ratio of the area of the photosurface to the perimeter of the photosurface is greater than or equal to a ratio threshold. This is because, generally, for most shapes of graphics, the ratio of the area of the graphic to the perimeter has a positive correlation with the size of the area, i.e., the larger the ratio of the area of the graphic to the perimeter, the larger the area of the graphic.

Exemplary, e.g. circular, having an area of π R ² The ratio of the area of the circle to the circumference is R/2, where R represents the radius. Since the ratio of the area of the circle to the circumference is only related to the radius, and the size of the area of the circle is only related to the radius, the ratio of the area of the circle to the circumference and the size of the area have a positive correlation, and if the ratio of the area of the circle to the circumference is defined, the size of the area of the circle is also defined. As another example, a square has an area a ² The ratio of the area of the square to the perimeter is a/4, and a represents the side length. Because the ratio of the area of the square to the perimeter is only related to the side length, and the area of the square is only related to the side length, the ratio of the area of the square to the perimeter and the size of the area have a positive correlation, and if the ratio of the area of the square to the perimeter is defined, the size of the area of the square is also defined.

According to an embodiment of the present disclosure, the ratio threshold is greater than or equal to 0.04mm.

According to the embodiment of the present disclosure, the area of the photosensitive surface of the present disclosure is a relatively large area, that is, the area of the photosensitive surface is a large area within an area range. This will be explained below.

First, the area of the photosensitive surface cannot be too small. Because the large-area photosensitive surface of the embodiment of the disclosure refers to the area of the photosensitive surface, so that the photosensitive surface can acquire the light intensity value of the emergent light emitted from the emitting position within the preset anti-shaking range, the large area of the large-area photosensitive surface of the embodiment of the disclosure is a large area for realizing anti-shaking, and meanwhile, the area of the photosensitive surface can be represented by the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface, so that the light intensity value of the emergent light emitted from the emitting position within the preset anti-shaking range can be acquired by the photosensitive surface, and under a normal condition, the ratio of the area of the photosensitive surface to the perimeter and the area of the photosensitive surface have a positive correlation relationship, so that if the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to a ratio threshold, the size of the area of the photosensitive surface is actually limited, that is, that the area of the photosensitive surface cannot be too small by the ratio of the area of the photosensitive surface to the perimeter being greater than or equal to the ratio threshold.

Secondly, the area of the photosensitive surface cannot be too large. The embodiment of the disclosure requires that the proportion of the average optical path of the emergent light received by the photosensitive surface in the target tissue layer to the total optical path is greater than or equal to a proportion threshold, and/or the area of the photosensitive surface is determined according to the tissue structure characteristics, which indicates that the area of the photosensitive surface cannot be too large.

It can be stated that the area of the photosensitive surface of the embodiment of the present disclosure is a relatively large area, i.e., a large area within the area range.

In addition, although the area of the photosensitive surface is large, the ratio of the area of the photosensitive surface to the circumference of the photosensitive surface is not large because the circumference of the photosensitive surface is also large, that is, the ratio of the area of the photosensitive surface to the circumference of the photosensitive surface is smaller than the threshold value of the ratio, and thus, it may be difficult for the absolute large-area photosensitive surface to meet the requirement of anti-shake. The situation that the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is smaller than the ratio threshold value due to the fact that the area of the photosensitive surface is too small and the perimeter of the photosensitive surface is large may also exist, and therefore the requirement for anti-shaking is difficult to meet due to the fact that the area of the photosensitive surface is too small.

According to the embodiment of the disclosure, the photosensitive surface is in contact with or not in contact with the surface of the detection area.

According to embodiments of the present disclosure, forms of tissue constituent detection may include contact detection and non-contact detection. Wherein, the contact detects and can avoid disturbing light to be received by the sensitization face, and then can improve and detect the precision. The non-contact detection can avoid the influence of interference factors such as temperature, pressure and the like on the detection result, and further can improve the detection precision.

If the light-sensing surface is arranged to contact the surface of the detection region, the tissue composition detection may be considered to be in the form of contact detection. If the light-sensing surface is arranged to be in non-contact with the surface of the detection region, the tissue composition detection may be considered to be in the form of a non-contact detection.

According to the embodiment of the disclosure, the distance between the photosensitive surface and the surface of the detection area is smaller than or equal to the first distance threshold, and the efficiency of receiving emergent light by the photosensitive surface is larger than or equal to the efficiency threshold.

According to the embodiment of the disclosure, since the photosensitive surface is made of the photosensitive material, the area of the photosensitive surface is continuous, so that the receiving of a large-range light intensity value can be realized, and the efficiency of receiving emergent light is improved. Based on this, even in the case of being close to the surface of the detection region, that is, in the case where the distance of the photosensitive surface from the surface of the detection region is less than or equal to the first distance threshold value, it is possible to achieve that the efficiency of receiving the outgoing light is greater than or equal to the efficiency threshold value.

According to an embodiment of the present disclosure, determining the concentration of the at least one measured tissue constituent based on the at least one output light intensity corresponding to the at least one preset wavelength may include the following operations.

In the case of each of the at least one measured tissue component, for each of at least one preset wavelength, a first output light intensity and a second output light intensity are determined from at least two output light intensities corresponding to the preset wavelength. And determining the concentration of the detected tissue component according to the first output light intensity and the second output light intensity corresponding to each preset wavelength.

According to the embodiment of the present disclosure, the average optical path of the outgoing light corresponding to the first output light intensity is different from the average optical path of the outgoing light corresponding to the second output light intensity. For each measured tissue component, the concentration of the measured tissue component can be determined according to the first output light intensity and the second output light intensity corresponding to each preset wavelength.

According to the embodiment of the present disclosure, determining the concentration of the measured tissue component according to the first output light intensity and the second output light intensity corresponding to the respective preset wavelengths may include the following operations.

And carrying out differential processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal. And determining the concentration of the detected tissue component according to the differential signals corresponding to the preset wavelengths.

According to the embodiments of the present disclosure, since the variation of the uncontrollable detection condition has a characteristic of being difficult to predict and uncontrollable, it is difficult to reduce the influence of the variation of the uncontrollable detection condition on the detection result in a manner of achieving reproducibility by employing an effective control method. In order to improve the detection accuracy, the inventors have found that the influence of variations in the uncontrollable detection conditions on the detection results can be reduced by using a reasonable mathematical algorithm so that the influence thereof on the detection results can be reduced to a negligible extent, i.e. so that the influence of variations in the uncontrollable detection conditions on the detection results is comparable to the level of the influence of random noise on the detection results.

In order to reduce the influence of the variation of the uncontrollable detection condition on the detection result, an interference suppression method can be adopted, wherein the interference suppression method can comprise a differential detection method. The differential detection method may include a time differential detection method and a position differential detection method. The reason why the differential detection method can reduce the influence of the variation of the uncontrollable detection condition on the detection result is that if the interference information carried by the output light intensities under different average light paths is basically the same, that is, the influence of the interference on the output light intensities under different average light paths is basically the same, the effective information carried by the output light intensities under different average light paths is different, so that the output light intensities under two average light paths (namely, the first output light intensity and the second output light intensity) can be subjected to differential processing to obtain a differential signal, and the concentration of the detected tissue component is determined according to the differential signal. Wherein the disturbance information may be understood as the response of the output light intensity to the disturbance. Valid information may be understood as the response of the output light intensity to the measured tissue composition.

According to an embodiment of the present disclosure, the difference processing of performing the difference processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength may include a hardware-aspect processing manner and a software-aspect processing manner. The processing manner in the aspect of hardware may include processing by using a differential circuit. The software-aspect processing may include performing a difference operation using a difference algorithm. The difference algorithm may include a direct difference operation and a logarithmic difference operation. The direct difference operation is to directly perform difference processing on the two parameters. The logarithmic difference operation means that firstly, the logarithm operation is carried out on the two parameters to obtain a parameter after the logarithm operation, and then the difference processing is carried out on the two parameters after the logarithm operation.

According to the embodiment of the disclosure, common-mode interference information can be effectively weakened through a differential detection method, and thus the detection precision is improved.

According to an embodiment of the present disclosure, performing a difference process on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a difference signal may include the following operations.

And processing the first output light intensity and the second output light intensity corresponding to the preset wavelength by using a differential circuit to obtain a differential signal.

According to the embodiment of the present disclosure, the differential processing of the first output light intensity and the second output light intensity may be implemented by using a differential circuit to directly obtain a differential signal.

And processing the first output light intensity and the second output light intensity corresponding to the preset wavelength by adopting a differential algorithm to obtain a differential signal.

According to an embodiment of the present disclosure, processing the first output light intensity and the second output light intensity corresponding to the preset wavelength by using a difference algorithm to obtain a difference signal may include the following operations.

And carrying out direct differential operation on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal.

And carrying out logarithm processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain first logarithm light intensity and second logarithm light intensity. And carrying out direct differential operation on the first logarithmic light intensity and the second logarithmic light intensity corresponding to the preset wavelength to obtain a differential signal.

According to an embodiment of the present disclosure, the first logarithmic light intensity represents a logarithm of the first output light intensity, and the second logarithmic light intensity represents a logarithm of the second output light intensity.

The differential signal can be determined by the following formula (1).

Wherein A is _D Which represents a differential signal, is shown,

represents a first output light intensity, is greater than or equal to>

Representing the second output light intensity. />

Represents the average light path corresponding to the first output light intensity, is>

Indicating the average optical path length corresponding to the second output light intensity.

According to the embodiment of the disclosure, the first output light intensity and the second output light intensity are acquired by the same or different similar photosensitive surfaces at different moments, wherein the first output light intensity is a systolic light intensity, the second output light intensity is a diastolic light intensity, the similar photosensitive surfaces comprise one or more photosensitive surfaces, and the similar photosensitive surfaces are used for outputting one output light intensity.

According to the embodiment of the disclosure, under the condition that the first output light intensity and the second output light intensity are acquired by the same or different photosensitive surfaces at different moments, the tissue component detection can be carried out by adopting a pulse wave-based time difference detection method.

The pulse, i.e. the arterial pulsation, means periodic contraction and relaxation along with the pulsation of the heart, the pressure in the aorta causes the diameter of the blood vessel to change in a pulsating manner, and the blood flow in the blood vessel also changes regularly and periodically along with the change. Each pulse waveform includes an ascending branch and a descending branch, wherein the ascending branch represents the dilation of the systolic ventricular artery and the descending branch represents the retraction of the diastolic ventricular artery. The contraction of the ventricles represents a period of pulsation.

According to the embodiments of the present disclosure, since the time difference detection method based on the pulse wave is adopted, it is necessary to use information of the pulse as much as possible, and therefore, in order to improve the detection accuracy, the light-sensing surface may be disposed at a position as close as possible to the target site (for example, the target blood vessel). That is, the analogous photosensitive surfaces for outputting the first output light intensity and the second output light intensity may be disposed at a position where the distance from the target portion is less than or equal to the fourth distance threshold. The fourth distance threshold may be zero, that is, the same type of photosensitive surface may be disposed on the target portion. The same type photosensitive surface for outputting the first output light intensity and the second output light intensity is arranged at a position where the distance from the target part is smaller than or equal to a fourth distance threshold, namely the distance from each photosensitive surface in the same type photosensitive surface for outputting the first output light intensity and the second output light intensity to the target part is smaller than or equal to the fourth distance threshold. The distance from each photosensitive surface in the same type of photosensitive surfaces to the target portion is smaller than or equal to the fourth distance threshold, and may be a distance from an edge of the photosensitive surface, which is farthest from the target portion, in the same type of photosensitive surfaces to the target blood vessel is smaller than or equal to the fourth distance threshold.

It should be noted that, with the pulse wave-based time difference detection method, it is necessary to use the pulse information as much as possible, which uses the useful information of the pulse as much as possible, and to reduce the adverse effect of the pulse on the detection by using the large-area photosurface as described above, which does not contradict the above-mentioned requirement. In addition, the first output light intensity may be a diastolic light intensity, and the second output light intensity may be a systolic light intensity. The first output light intensity and the second output light intensity corresponding to the preset wavelength may be output light intensities in the same pulse period or output light intensities in different pulse periods.

According to the embodiment of the disclosure, a first output light intensity corresponding to a preset wavelength is acquired by a first similar photosensitive surface corresponding to the preset wavelength, and a second output light intensity corresponding to the preset wavelength is acquired by a second similar photosensitive surface corresponding to the preset wavelength, wherein the first similar photosensitive surface comprises one or more photosensitive surfaces, and the second similar photosensitive surface comprises one or more photosensitive surfaces.

According to the embodiment of the disclosure, for a preset wavelength, a first similar photosensitive surface and a second similar photosensitive surface corresponding to the preset wavelength are provided, wherein the first similar photosensitive surface is used for outputting a first output light intensity corresponding to the preset wavelength, and the second similar photosensitive surface is used for outputting a second output light intensity corresponding to the preset wavelength. The first and second homogeneous photosurfaces may each comprise one or more photosurfaces.

According to an embodiment of the present disclosure, the first output light intensity and the second output light intensity may be processed using a position differential detection method to determine the concentration of the measured tissue constituent.

According to the embodiments of the present disclosure, since it is necessary to avoid the target site (for example, the target blood vessel) as much as possible by using the position difference detection method, the light-sensing surface may be disposed at a position as far as possible from the target site in order to improve the detection accuracy. That is, the first homogeneous photosurface for outputting the first output light intensity may be located at a distance from the target portion which is greater than or equal to the fifth distance threshold, that is, the distance from each photosurface in the first homogeneous photosurface to the target portion is greater than or equal to the fifth distance threshold. The distance from each photosensitive surface in the first homogeneous photosensitive surface to the target portion may be greater than or equal to a fifth distance threshold, and the distance from the edge of the photosensitive surface closest to the target portion in the first homogeneous photosensitive surface to the target portion may be greater than or equal to the fifth distance threshold. Or the first homogeneous photosensitive surface is not in contact with the target part, and the distance between the center of the photosensitive surface closest to the target part in the first homogeneous photosensitive surface and the target part is greater than or equal to a fifth distance threshold value. And setting the photosensitive surface for outputting the second output light intensity at a position where the distance from the target part is greater than or equal to a sixth distance threshold. For the understanding that the second homogeneous photosensitive surface for outputting the second light intensity is disposed at the position where the distance from the target portion is greater than or equal to the sixth distance threshold, reference may be made to the description of the first homogeneous photosensitive surface for outputting the first output light intensity, and details thereof are not repeated herein.

According to the embodiment of the disclosure, the first similar photosensitive surface and the second similar photosensitive surface are the same similar photosensitive surface, and the emergent light received by the first similar photosensitive surface and the second similar photosensitive surface is obtained by transmitting incident light after the incident light is incident from different incident positions.

According to an embodiment of the present disclosure, the first and second homogeneous photosensitive surfaces are different homogeneous photosensitive surfaces.

According to the embodiment of the disclosure, the incident positions of the incident light include at least two, the first similar photosurfaces and the second similar photosurfaces may be the same photosurfaces, except that if the similar photosurfaces are the similar photosurfaces for receiving the emergent light corresponding to the first output light intensity, that is, the same photosurfaces are used as the first similar photosurfaces, the incident position of the emergent light is the first incident position. If the same kind of photosensitive surface is used for receiving emergent light corresponding to the second output light intensity, namely used as a second same kind of photosensitive surface, the incident position of the emergent light is a second incident position, and the first incident position and the second incident position are different incident positions.

According to an embodiment of the present disclosure, the first and second homogeneous photosensitive surfaces may also be different homogeneous photosensitive surfaces.

According to the embodiment of the disclosure, the average optical path of the emergent light received by different photosensitive positions of each photosensitive surface in the first homogeneous photosensitive surface belongs to a first average optical path range, wherein the first average optical path range is determined according to a first optical path average value, and the first optical path average value is an average value calculated according to the average optical path of the emergent light received by each photosensitive position of the first homogeneous photosensitive surface. The average optical path of the emergent light received by different photosensitive positions of each photosensitive surface in the second similar photosensitive surface belongs to a second average optical path range, wherein the second average optical path range is determined according to a second optical path average value, and the second optical path average value is an average value obtained by calculating the average optical path of the emergent light received by each photosensitive position of the second similar photosensitive surface.

According to the embodiment of the disclosure, in order to improve the detection accuracy of tissue composition detection by using a position difference-based detection method, it is necessary to ensure that the emergent light received by the first similar photosensitive surface has a characteristic of a short optical path as much as possible, and the emergent light received by the second similar photosensitive surface also has a characteristic of a short optical path. The short path length is understood to mean that the average path length of the outgoing light is within the range of the average path length.

Aiming at the first similar photosurfaces, the average optical path of emergent light received by different photosites of each photosurface in the first similar photosurface belongs to the range of the first average optical path. Wherein the first average optical path range is determined as follows. And determining a first optical path average value of the average optical paths of the emergent light received by all the photosensitive positions of the first similar photosensitive surface, and determining a first optical path variation amplitude. And determining a first average optical path range according to the first optical path average value and the first optical path variation amplitude. For example, if the first path average value is b and the first path variation amplitude is ± 40%, the first average path range may be greater than or equal to 0.6b and less than or equal to 1.4b.

And aiming at the second similar photosensitive surface, the average optical path of the emergent light received by different photosensitive positions of each photosensitive surface in the second similar photosensitive surface belongs to the second average optical path range. Wherein the second average optical path range is determined as follows. And determining a second optical path average value of the average optical paths of the emergent light received by all the photosensitive positions of the second similar photosensitive surface, and determining a second optical path variation amplitude. And determining a second average optical path range according to the second optical path average value and the second optical path variation amplitude.

According to an embodiment of the present disclosure, an absolute value of a difference value of the first optical path average value and the second optical path average value belongs to the first optical path difference range.

According to the embodiment of the present disclosure, in order to improve the detection accuracy of tissue composition detection based on the differential detection method, it is necessary to set a first homogeneous photosensitive surface and a second homogeneous photosensitive surface within a suitable position range. The following description will be given taking the measured tissue composition as blood sugar. For the tissue to be measured to be classified as blood sugar, the target tissue layer is the dermis layer, and the required output light intensity is the output light intensity mainly carrying the tissue composition information in the dermis layer.

First, if the distance from the position of the photosensitive surface to the center of the incident light is too small, the intensity of the output light of the outgoing light will mainly carry information on the tissue composition in the epidermis layer. If the distance between the position of the photosensitive surface and the center of the incident light is too large, the output light intensity of the emergent light mainly carries the tissue composition information in the subcutaneous fat layer. The dermis is located between the epidermis layer and the subcutaneous fat layer, so that the arrangement positions of the first similar photosensitive surface and the second similar photosensitive surface need to be selected in a proper position range, and the distance between the first similar photosensitive surface and the second similar photosensitive surface cannot be too large.

Secondly, although the differential detection method can effectively reduce the common-mode interference, the differential detection method can also lose a part of effective information, namely blood glucose information, while reducing the common-mode interference. If the two locations are in close proximity, then valid information may be lost altogether. Therefore, the arrangement positions of the first similar photosensitive surface and the second similar photosensitive surface need to be selected in a proper position range, and the distance between the first similar photosensitive surface and the second similar photosensitive surface cannot be too small.

In order to realize that the first similar photosensitive surface and the second similar photosensitive surface are arranged in a reasonable position range, the detection method can be determined according to an effective information detection principle, a differential detection precision optimization principle and an interference signal effective elimination principle. The effective information detection principle may mean that the emergent light at two positions can carry tissue composition information in a target tissue layer as much as possible, and therefore, the two positions should be within a reasonable position range. The principle of optimizing the precision of differential detection may mean that there should be a certain distance between two positions to ensure that as much valid information as possible remains after the difference. The principle of effectively eliminating the interference signal may mean that the distance between the two positions should be as small as possible to improve the effect of eliminating the common mode interference by the differential detection method.

And setting a first similar photosurface and a second similar photosurface in a reasonable position range, and reflecting the first similar photosurface and the second similar photosurface on the optical path, wherein the absolute value of the difference between a first optical path average value corresponding to the first similar photosurface and a second optical path average value corresponding to the second similar photosurface belongs to a first optical path difference range. Wherein, the first optical path difference range is determined according to the optimal differential optical path. The optimal differential optical path may be determined according to at least one of the three principles described above.

It can be understood that the requirements for the position setting of the first similar photosensitive surface and the second similar photosensitive surface also require that the area of the photosensitive surfaces cannot be too large, otherwise the differential effect will be affected, and the detection precision will be affected.

According to the embodiment of the present disclosure, the first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range.

According to the embodiment of the disclosure, in order to achieve setting of the first similar photosensitive surface and the second similar photosensitive surface within a reasonable position range as much as possible and reflect on the optical path, it is further required to ensure that the first average optical path range is less than or equal to the first optical path difference range and the second average optical path range is less than or equal to the first optical path difference range as much as possible. Therefore, the absolute value of the difference between the first optical path average value corresponding to the first similar photosensitive surface and the second optical path average value corresponding to the second similar photosensitive surface belongs to a first optical path difference range, the first average optical path range is smaller than or equal to the first optical path difference range, and the second average optical path range is smaller than or equal to the first optical path difference range.

According to an embodiment of the present disclosure, the first optical path difference range is determined according to an optimal differential optical path corresponding to a preset wavelength.

According to the embodiments of the present disclosure, in the case where the detection region of the living body to be detected is determined, there is an optimum differential sensitivity corresponding to the preset wavelength, wherein the optimum differential sensitivity may represent a sensitivity corresponding to a time when a change in the differential signal due to a change in the concentration of a unit of the tissue composition to be detected is the largest, the optimum differential optical length may be determined from the optimum differential sensitivity, that is, the optimum differential optical length may be determined according to the principle of optimization of the precision of differential detection, and thus, the optical length corresponding to the optimum differential sensitivity may be referred to as the optimum differential optical length.

According to the embodiment of the disclosure, after determining the optimal differential optical path corresponding to the preset wavelength, the up-down adjustment amplitude may be set, and the first optical path difference range corresponding to the preset wavelength is determined according to the optimal differential optical path corresponding to the preset wavelength and the up-down adjustment amplitude.

According to the embodiment of the disclosure, the source detection distance from each photosurface in the first homogeneous photosurface corresponding to the preset wavelength to the center of the incident light is within the preset source detection distance range corresponding to the preset wavelength, wherein the preset source detection distance range is determined according to the source detection distance from the floating reference position corresponding to the preset wavelength to the center of the incident light.

According to an embodiment of the present disclosure, in order to further improve the detection accuracy, the position of the photosensitive surface may be set based on a floating reference method. The floating reference method will be described below.

For a detected living body, when incident light enters tissues, absorption and scattering actions can occur, the absorption action can directly cause light energy attenuation, the scattering action can influence the distribution of emergent light by changing the transmission direction of photons, and the distribution of the emergent light is the result of the combined action of the incident light and the emergent light. Based on the floating reference method, there is a position from the center of the incident light for the measured tissue component where the degrees of influence of the absorption and scattering effects on the output light intensity of the outgoing light are the same and opposite in direction, and therefore, the outgoing light is not sensitive to the concentration change of the measured tissue component. A position having the above-described characteristics may be referred to as a reference position (or referred to as a reference position). The output intensity of the emergent light at the reference position reflects the response to disturbances other than the measured tissue component during the detection process. Meanwhile, there is also a position from the center of the incident light for the measured tissue component, and the sensitivity of the output light intensity of the outgoing light at the position to the concentration change of the measured tissue component is greater than or equal to the sensitivity threshold. A position having the above-described characteristics may be referred to as a detection position. The output light intensity of the emergent light at the detection position reflects the response to the detected tissue component in the detection process and the response to other interference except the detected tissue component. Further, the reference position and the detection position vary depending on the wavelength, the living body to be detected, and the detection region, and thus the reference position can be referred to as a floating reference position.

According to the embodiments of the present disclosure, since the output light intensity of the outgoing light emitted at the floating reference position mainly carries the response to the interference other than the measured tissue component during the detection process, the output light intensity of the outgoing light emitted from the floating reference position can be introduced into the differential detection to weaken the common mode interference to the maximum extent and lose the effective information to a smaller extent. Based on the above, in the case that the detection area of the detected living body is determined, for each preset wavelength, the source detection distance from at least one photosensitive surface in the M photosensitive surfaces to the center of the incident light is within the preset source detection distance range corresponding to the preset wavelength, and the preset source detection distance range is determined according to the source detection distance from the floating reference position corresponding to the preset wavelength to the center of the incident light. In an embodiment of the present disclosure, a source detection distance of each photosurface of the first homogeneous photosurface from a center of incident light may be within a preset source detection distance range corresponding to a preset wavelength.

Illustratively, for example, the detection area B of the detected living body A and the preset wavelength lambda ₁ The distance between the corresponding floating reference position and the center of the incident light is 1.7mm, and the distance is equal to the preset wavelength lambda ₁ The corresponding preset source probe distance range may be 1.5mm to 1.9mm.

Based on the above, the same kind of photosensitive surface corresponding to the reference position and the same kind of photosensitive surface corresponding to the detection position can be determined, the output light intensity collected by the same kind of photosensitive surface corresponding to the reference position is referred to as a first output light intensity, and the output light intensity collected by the same kind of photosensitive surface corresponding to the detection region is referred to as a second output light intensity. Or, the output light intensity collected by the same kind of photosensitive surface corresponding to the detection region is referred to as a first output light intensity, and the output light intensity collected by the same kind of photosensitive surface corresponding to the reference position is referred to as a second output light intensity.

In the case of each of the at least one measured tissue components, for each of the at least one preset wavelength, a third output light intensity is determined from the at least one output light intensity corresponding to the preset wavelength. And carrying out differential processing on the third output light intensities corresponding to different preset wavelengths to obtain at least one differential signal. The concentration of the measured tissue constituent is determined based on the at least one differential signal.

According to an embodiment of the present disclosure, the third output light intensity may be processed using a wavelength differential detection method to determine the concentration of the measured tissue constituent. If the following conditions are met, the tissue composition detection can be carried out by adopting a wavelength differential detection method, so that the common-mode interference is eliminated, meanwhile, enough effective information can be kept, and the detection precision is improved.

First, for each tissue component to be measured, the influence of the same disturbance (such as temperature or pressure) on the output light intensity at two preset wavelengths is consistent or substantially consistent.

Secondly, the sensitivity of the output light intensity under two preset wavelengths to the change of the concentration of the detected tissue components has larger difference.

And under the condition that the preset wavelength is determined, determining a third output light intensity from at least one output light intensity corresponding to the preset wavelength. Thereby a third output light intensity for each preset wavelength can be obtained. For two preset wavelengths, the two third output light intensities may be subjected to difference processing to obtain a difference signal.

According to the embodiment of the present disclosure, the differential processing of the two third output light intensities may include the following operations. And processing the two third output light intensities by adopting a differential circuit to obtain a differential signal. Or, performing differential operation on the two third output light intensities by adopting a differential algorithm to obtain a differential signal. And performing a difference operation on the two third output light intensities by using a difference algorithm to obtain a difference signal, wherein the following operation can be performed. And carrying out direct differential operation on the two third output light intensities to obtain a differential signal. Or, the two third output light intensities are respectively subjected to logarithm processing to obtain two logarithm light intensities, and the two logarithm light intensities are subjected to direct differential operation to obtain a differential signal.

According to an embodiment of the present disclosure, determining the concentration of the measured tissue constituent according to the differential signal corresponding to each preset wavelength may include the following operations.

And carrying out direct differential operation on the differential signals corresponding to different preset wavelengths to obtain at least one wavelength differential signal. And determining the concentration of the detected tissue component according to the at least one wavelength differential signal.

According to embodiments of the present disclosure, the differential signal may be processed using a wavelength differential detection method to determine the concentration of the measured tissue constituent. If the following conditions are met, the tissue composition detection can be carried out by adopting a wavelength differential detection method, so that the common-mode interference is eliminated, meanwhile, enough effective information can be kept, and the detection precision is improved.

First, for each tissue component to be measured, the influence of the same disturbance (e.g., temperature or pressure) on the differential signal at two preset wavelengths is consistent or substantially consistent.

Secondly, the sensitivity of the differential signals under the two preset wavelengths to the concentration change of the detected tissue components has larger difference.

For two preset wavelengths, the two differential signals can be subjected to direct differential operation to obtain wavelength differential signals. And determining the concentration of the detected tissue component according to the at least one wavelength differential signal.

In the case of each of the at least one measured tissue component, for each of the at least one preset wavelength, determining at least one superimposed light intensity corresponding to the preset wavelength, wherein the superimposed light intensity is obtained by adding a plurality of output light intensities corresponding to the preset wavelengths. And determining the concentration of the detected tissue component according to at least one superposed light intensity corresponding to each preset wavelength.

According to the embodiment of the disclosure, when the concentration of the detected tissue component is determined, the acquired data can be flexibly utilized according to actual conditions, such as a small numerical value of single output light intensity or a low signal-to-noise ratio of the output light intensity, so as to improve the detection accuracy.

Based on the above, for each measured tissue component, in the case of determining the preset wavelength, at least one superimposed light intensity corresponding to the preset wavelength is determined, and the concentration of the measured tissue component is determined according to the at least one superimposed light intensity corresponding to each preset wavelength, wherein the superimposed light intensity may be obtained by adding a plurality of output light intensities. The output light intensity is the intensity of diffuse light (i.e., the outgoing light).

In the case of each of the at least one measured tissue components, for each of the at least one preset wavelength, a fourth output light intensity is determined from the at least one output light intensity corresponding to the preset wavelength. And determining the concentration of the detected tissue component according to the fourth output light intensity corresponding to each preset wavelength.

According to the embodiment of the disclosure, the tissue component detection can be performed by adopting a non-differential detection method, that is, the concentration of the detected tissue component is determined according to the fourth output light intensity corresponding to each preset wavelength.

According to the embodiment of the disclosure, the fourth output light intensity corresponding to the preset wavelength is acquired by the same kind of photosensitive surface corresponding to the preset wavelength, and a difference value between an average optical path of the emergent light received by different photosensitive positions of each photosensitive surface in the same kind of photosensitive surface and an optimal optical path corresponding to the preset wavelength belongs to the second optical path difference range.

According to the embodiment of the disclosure, in order to improve the detection accuracy, in the case that the detection area of the detected living body is determined, for each preset wavelength, the average optical path of the outgoing light received at different photosensitive positions in the same type photosensitive surface for acquiring the third output light intensity may be made to approach the optimal optical path corresponding to the preset wavelength, that is, the absolute value of the difference between the average optical path of the outgoing light received at different photosensitive positions in the same type photosensitive surface for acquiring the third output light intensity and the optimal optical path corresponding to the preset wavelength is smaller than or equal to the second optical path difference range. The optimal optical path corresponding to the preset wavelength can be understood as the optical path corresponding to the maximum sensitivity of the detected tissue component at the preset wavelength.

According to an embodiment of the present disclosure, each photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface, and the shapes of the different photosensitive surfaces are the same or different.

According to an embodiment of the present disclosure, each photosensitive surface may be made of a photosensitive material. The annular photosensitive surface can avoid the problem of azimuth positioning, and can realize the design of a larger area in a smaller source detection distance range. It should be noted that, since the source-probe distance is usually a relatively important physical quantity in the detection of the living tissue components, it is very meaningful to design a relatively large area within a relatively small source-probe distance.

According to the embodiment of the present disclosure, in some cases, the non-annular photosurface is adopted to have the following beneficial effects.

First, because the detection result is influenced by the detection area, if the photosurface is disposed in the detection area favorable for detection, compared with the photosurface disposed in the detection area favorable for detection with interference, the detection result obtained by disposing the photosurface in the detection area favorable for detection is better, and therefore, the photosurface can be disposed in a proper position according to the tissue structure characteristics. The non-annular photosensitive surface can easily avoid a detection area with interference on detection, such as a blood vessel or a wound area, so that the non-annular photosensitive surface has a good effect.

Secondly, due to the non-uniformity of the tissue, the transmission paths of the same incident light in the tissue may be different, and the average optical paths corresponding to the emergent light at different emitting positions are different. Taking the blood sugar as an example of the organization to be measured, the dermis is the main source of the blood sugar signal, so that the emergent light is the emergent light which is mainly obtained after transmission in the dermis, and accordingly, certain requirements are provided for the average optical path corresponding to the emergent light.

Assuming that the annular light-sensing surface with the corresponding size is designed according to the requirement for the average optical path, it can be considered that the average optical paths corresponding to the emergent light received by different light-sensing positions of the annular light-sensing surface are basically similar and mainly the emergent light passing through the dermis layer, and the average optical path is within the average optical path range C. In this case, if the skin tissue is uniform, the above conclusion is in line with the actual situation. However, since the skin tissue is not uniform, the average optical path difference corresponding to the outgoing light received by different photosensitive positions of the same annular photosensitive surface is large, if the average optical paths corresponding to the outgoing light received by a part of the photosensitive positions of the annular photosensitive surface are substantially similar and are within the average optical path range C, the average optical path corresponding to the outgoing light received by another part of the photosensitive positions of the annular photosensitive surface is larger than the difference and is not within the average optical path range C. Because the average optical path of the emergent light in the average optical path range C can indicate that the emergent light mainly passes through the corium layer, the emergent light out of the average optical path range C may not mainly pass through the corium layer, and meanwhile, the annular photosensitive surface outputs an output light intensity, the quality of signals of the output light intensity obtained by adopting the annular photosensitive surface is not high under the condition that skin tissues are not uniform, and the detection precision is further influenced.

The non-annular photosensitive surfaces may be set according to actual conditions, and in the above example, assuming that the average optical path that is not within the average optical path range C is within the average optical path range D, two non-annular photosensitive surfaces may be used, where one non-annular photosensitive surface is used to receive the light intensity value of the outgoing light whose average optical path is within the average optical path range C of the outgoing light, and the other non-annular photosensitive surface is used to receive the light intensity value of the outgoing light whose average optical path is within the average optical path range D of the outgoing light, and the output light intensities of the two non-annular photosensitive surfaces are consistent with actual values, which is favorable for ensuring detection accuracy.

Thirdly, when the time difference detection method based on the pulse wave is adopted for the tissue component detection, the pulse signal is required to be fully utilized, namely, the difference between the light intensity in the systolic period and the light intensity in the diastolic period is as large as possible. Under the condition, most of the annular photosensitive surface is not positioned above the blood vessel, so that the pulse signal acquisition effect is influenced, and the difference degree between the light intensity in the contraction phase and the light intensity in the diastole phase is reduced. Therefore, the difference degree of the light intensity in the contraction period and the light intensity in the relaxation period obtained by adopting the annular photosensitive surface is smaller than that of the light intensity in the contraction period and the light intensity in the relaxation period obtained by adopting the non-annular photosensitive surface.

Fourthly, due to the influence of tissue heterogeneity and physiological background variation on emergent light, the average optical paths of the emergent light received by different photosurfaces with the same source detection distance from the center of incident light may have difference, so that the output light intensities collected by different photosurfaces with the same source detection distance from the center of the incident light can be adopted to carry out differential operation for tissue component detection. The non-annular photosensitive surface can be realized, namely at least two non-annular photosensitive surfaces are discretely arranged by taking the center of incident light as the center aiming at the same source detection distance so as to realize the output of two output light intensities.

Fifthly, the manufacturing process difficulty is low, and the manufacturing cost is low.

The fourth aspect is explained below with reference to fig. 5. Fig. 5 schematically illustrates a schematic diagram of a differential detection according to an embodiment of the disclosure. As shown in fig. 5, fig. 5 includes four sector ring photosensitive surfaces, which are sector ring photosensitive surface 1, sector ring photosensitive surface 2, sector ring photosensitive surface 3, and sector ring photosensitive surface 4, where the four sector ring photosensitive surfaces are used separately, and each sector ring photosensitive surface has a corresponding output light intensity. The centers of the four fan-ring photosurfaces are the same distance from the center of incident light, namely the same source-detecting distance is obtained. Due to tissue heterogeneity, average optical paths corresponding to emergent light received by the sector ring photosensitive surface 1 and the sector ring photosensitive surface 2 are different, so that differential operation can be performed according to output light intensity collected by the sector ring photosensitive surface 1 and output light intensity collected by the sector ring photosensitive surface 2, and differential detection is realized.

According to an embodiment of the present disclosure, the non-annular photosensitive surface includes a sector ring photosensitive surface, a circular photosensitive surface, a sector photosensitive surface, an oval photosensitive surface, or a polygonal photosensitive surface.

According to an embodiment of the present disclosure, the polygonal photosensitive surface includes a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

According to the embodiment of the disclosure, the central angle can be designed according to actual conditions to obtain the corresponding sector ring photosurface. For example, a sector ring photosurface with a central angle of 90 °, a sector ring photosurface with a central angle of 180 °, and a sector ring photosurface with a central angle of 45 °.

Fig. 6 schematically illustrates a schematic view of an annular photosurface according to an embodiment of the disclosure. Fig. 7 schematically illustrates a schematic view of a sector ring photosurface according to an embodiment of the disclosure. Fig. 8 schematically illustrates a schematic view of a circular photosurface according to an embodiment of the disclosure. Fig. 9 schematically illustrates a schematic diagram of a square photosurface according to an embodiment of the disclosure.

According to the embodiment of the disclosure, the same-type photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface, wherein the same-type photosensitive surface includes one or more photosensitive surfaces, and the same-type photosensitive surface is used for outputting an output light intensity.

According to the embodiments of the present disclosure, the similar photosensitive surface may be an annular photosensitive surface or a non-annular photosensitive surface, that is, the similar photosensitive surface may be an annular photosensitive surface or a non-annular photosensitive surface as a whole. Depending on the number of photosensitive surfaces that a similar type of photosensitive surface comprises, it may be determined whether the shape as a whole is formed by one single photosensitive surface or by a combination of a plurality of photosensitive surfaces. Wherein, each photosensitive surface in the same type of photosensitive surface can be an annular photosensitive surface or a non-annular photosensitive surface.

According to the embodiment of the present disclosure, the similar photosensitive surfaces are annular photosensitive surfaces, and may include: in the case where the similar photosensitive surface includes one photosensitive surface, the similar photosensitive surface is an independent annular photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is an annular photosensitive surface formed by combining the plurality of photosensitive surfaces. The similar photosensitive surface is a non-annular photosensitive surface and can comprise: in the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed according to a combination of the plurality of photosensitive surfaces.

According to the embodiment of the disclosure, the plurality of photosensitive surfaces participating in combination are closely arranged to ensure that no gap exists between the adjacent photosensitive surfaces as much as possible. Because the circular photosensitive surface or the square photosensitive surface is common at present, the manufacturing process difficulty is low, the manufacturing cost is low, photosensitive surfaces with other shapes are generally required to be customized, the manufacturing process difficulty is high, and the manufacturing cost is high, therefore, if the manufacturing cost is limited, a plurality of circular photosensitive surfaces and/or a plurality of square photosensitive surfaces can be combined to form the same type of photosensitive surfaces with other shapes by adopting a combined mode. Wherein the square shape comprises a square or a rectangle.

The manufacturing cost of the photosensitive surface is also related to the size of the area of the photosensitive surface, and generally, the larger the area of the photosensitive surface, the higher the manufacturing cost. If a larger-area photosurface is needed and a plurality of photosurfaces with smaller areas exist at present, the plurality of photosurfaces with smaller areas can be combined to obtain the larger-area photosurface in order to reduce the manufacturing cost.

According to the embodiment of the disclosure, under the condition that it is determined that the distance between the similar photosensitive surface and the target part is greater than or equal to the second distance threshold, the similar photosensitive surface comprises an annular photosensitive surface, a fan-shaped photosensitive surface, a circular photosensitive surface or a square photosensitive surface.

According to the embodiment of the disclosure, under the condition that the distance from the similar photosensitive surface to the target part is determined to be greater than or equal to the second distance threshold, the photosensitive surface with the proper shape can be selected according to the jitter condition of the actual emergent light, so that the adverse effect of jitter on detection is weakened to the greatest extent.

The target site may be a site where shaking occurs. Since one of the sources causing jitter is pulse beat, which is related to blood vessels, the target site may be a blood vessel. Generally, the jitter distribution of the emergent light close to the blood vessel has a certain directivity, while the jitter distribution of the emergent light far away from the blood vessel is relatively uniform and has no directivity.

If the similar photosensitive surface is far away from the target part (such as a target blood vessel), the jitter distribution of the emergent light can be relatively uniform, and in this case, an annular photosensitive surface, a fan-shaped photosensitive surface, a circular photosensitive surface or a square photosensitive surface can be selected. The distance of the same type of photosensitive surfaces from the target portion may be understood as the distance of each of the same type of photosensitive surfaces from the target portion being greater than or equal to the second distance threshold. The distance between each photosensitive surface of the same type of photosensitive surfaces and the target portion is greater than or equal to the second distance threshold, where the distance between the edge of the photosensitive surface closest to the target portion in the same type of photosensitive surfaces and the target portion is greater than or equal to the second distance threshold, or the same type of photosensitive surfaces are not in contact with the target portion, and the distance between the center of the photosensitive surface closest to the target portion in the same type of photosensitive surfaces and the target portion is greater than or equal to the second distance threshold.

Under the condition that the similar photosurfaces are far away from the target part, if the average optical path of the emergent light received by different photosurfaces in each photosurface of the similar photosurfaces is smaller than or equal to the optical path threshold value, the jitter condition of the emergent light can be shown to be influenced by the size of the optical path, wherein the larger the average optical path of the emergent light is, the more obvious the jitter condition of the emergent light is, and otherwise, the less obvious the jitter condition of the emergent light is. In this case, the arc length corresponding to a position farther from the center of the incident light may be designed to be longer, whereby an annular photosensitive surface, a fan-ring photosensitive surface, or a fan-shaped photosensitive surface may be selected.

Under the condition that the similar photosurfaces are far away from the target part, if the average optical path of the emergent light received by different photosurfaces in the similar photosurfaces is larger than the optical path threshold, the jitter condition of the emergent light is almost irrelevant to the size of the optical path. In this case, a circular photosensitive surface or a square photosensitive surface may be selected.

According to the embodiment of the disclosure, in the case that the same kind of photosensitive surface is a sector ring photosensitive surface, if the same kind of photosensitive surface includes one photosensitive surface, the sector ring photosensitive surface is an independent sector ring photosensitive surface. If the same type of photosensitive surface comprises a plurality of photosensitive surfaces, the sector ring photosensitive surface is a photosensitive surface formed by combining the plurality of photosensitive surfaces. Similarly, the same type of photosensitive surface may be formed independently or combined to form the same type of photosensitive surface in the case that the same type of photosensitive surface includes an annular photosensitive surface, a circular photosensitive surface, a square photosensitive surface, or a sector photosensitive surface.

It should be noted that, because the circular photosensitive surface or the square photosensitive surface is common at present, the manufacturing process difficulty is small, the manufacturing cost is low, and the photosensitive surfaces of other shapes generally need to be customized, the manufacturing process difficulty is large, and the manufacturing cost is high, if the manufacturing cost is limited, the similar photosensitive surface includes the circular photosensitive surface or the square photosensitive surface under the condition that the distance from the similar photosensitive surface to the target position is greater than or equal to the second distance threshold.

According to the embodiment of the disclosure, in the case that it is determined that the distance from the same type of photosensitive surface to the target portion is less than or equal to the third distance threshold, the shape of the same type of photosensitive surface is determined according to the jitter distribution of the outgoing light.

According to the embodiment of the present disclosure, if the similar photosensitive surface is close to the target portion (for example, the target blood vessel), it can be said that the jitter distribution of the outgoing light has a certain directivity. In this case, the shape of the same-type photosensitive surface may be made to be determined in accordance with the jitter distribution of the outgoing light, and optionally, the shape of the same-type photosensitive surface and the jitter distribution of the outgoing light are similar patterns. For example, if the jitter distribution of the outgoing light is an elliptical shape, the shape of the same type of photosensitive surface may be designed to be an elliptical photosensitive surface. Alternatively, if the jitter distribution of the outgoing light is rectangular, the shape of the similar photosensitive surface may be designed to be a rectangular photosensitive surface. Or, if the jitter distribution of the emergent light is rhombic, the shape of the same type of photosensitive surface can be designed to be a rhombic photosensitive surface.

According to an embodiment of the disclosure, the jitter distribution of the outgoing light includes a jitter distribution decomposed into a jitter distribution along a first direction and a jitter distribution along a second direction, the first direction and the second direction are perpendicular to each other, a ratio of a length of the same type of photosensitive surface along the first direction to a length of the same type of photosensitive surface along the second direction is determined according to a ratio of a jitter amplitude of the outgoing light along the first direction to a jitter amplitude of the outgoing light along the second direction, and the jitter amplitude of the outgoing light along the first direction is the largest.

According to the embodiment of the disclosure, if the jitter distribution of the outgoing light includes jitter distributions along two mutually perpendicular directions, where the jitter distributions of the two mutually perpendicular directions are obtained by decomposing jitter of the outgoing light into the two mutually perpendicular directions, the two mutually perpendicular directions are respectively referred to as a first direction and a second direction, where jitter amplitude of the outgoing light along the first direction is the largest, a ratio of a length of the same type of photosensitive surface along the first direction to a length of the same type of photosensitive surface along the second direction may be set according to a ratio of jitter amplitude of the outgoing light along the first direction to the second direction, and the ratio of the length of the same type of photosensitive surface along the first direction to the length of the same type of photosensitive surface along the second direction may be greater than or equal to the ratio of jitter amplitude of the outgoing light along the first direction to the second direction.

For example, if the first direction and the second direction are the Y-axis direction and the X-axis direction in a rectangular coordinate system, respectively, the ratio of the jitter amplitude of the outgoing light in the Y-axis direction to the jitter amplitude in the X-axis direction can be expressed as

The ratio of the length of the same type of photosensitive surface along the Y-axis direction to the length along the X-axis direction can be expressed as->

Then->

According to the embodiment of the disclosure, the similar photosensitive surface comprises a long rectangular photosensitive surface or an oval photosensitive surface, the ratio of the length to the width of the rectangular photosensitive surface is determined according to the ratio of the jitter amplitude of the emergent light in the first direction to the jitter amplitude of the emergent light in the second direction, and the ratio of the long axis to the short axis of the oval photosensitive surface is determined according to the ratio of the jitter amplitude of the emergent light in the first direction to the jitter amplitude of the emergent light in the second direction.

According to an embodiment of the disclosure, if the distance between the similar photosensitive surface and the target portion is less than or equal to the third distance threshold, the jitter distribution of the outgoing light includes a jitter distribution decomposed into a first direction and a second direction, and the first direction and the second direction are perpendicular to each other, the similar photosensitive surface may include a rectangular photosensitive surface or an elliptical photosensitive surface. The ratio of the length to the width of the rectangular photosensitive surface is larger than or equal to the ratio of the jitter amplitude of the emergent light along the first direction to the jitter amplitude of the emergent light along the second direction. The ratio of the long axis to the short axis of the elliptic photosensitive surface is larger than or equal to the ratio of the jitter amplitude of the emergent light along the first direction to the jitter amplitude of the emergent light along the second direction.

According to the embodiment of the disclosure, each output light intensity is processed according to the light intensity value of the emergent light collected by one or more photosensitive surfaces, and the following operations can be included.

One or more photosurfaces are used in combination to output an output light intensity. Or under the condition that each photosensitive surface in one or more photosensitive surfaces is used independently, the light intensity value of emergent light collected by each photosensitive surface is calculated to obtain output light intensity.

According to the embodiments of the present disclosure, the photosensitive surface for outputting an output light intensity is referred to as a similar photosensitive surface, and the similar photosensitive surface may include one or more photosensitive surfaces. The condition that different photosensitive surfaces are used in combination may be that the average optical path of the outgoing light received by each photosensitive surface is within the average optical path range. The average optical path range may be a range composed of greater than or equal to the first average optical path threshold and less than or equal to the second average optical path threshold. The first average optical path threshold and the second average optical path threshold may be determined according to an optical path average value and an optical path variation amplitude. The average value of the optical paths is an average value calculated according to the average optical paths of emergent light received by all photosensitive positions of the same type of photosensitive surfaces.

The photosensitive surface is usually used in conjunction with an amplifying circuit corresponding to the photosensitive surface to output a light intensity value. In order to enable the same type of photosensitive surfaces to output relatively accurate output light intensity, the product of the photoresponse rate of each photosensitive surface in the same type of photosensitive surfaces and the amplification factor of the amplifying circuit matched with the photosensitive surface is required to be a preset value, and under the condition that the photoresponse rate of each photosensitive surface and the amplification factor of the amplifying circuit matched with the photosensitive surface are ensured to be the same preset value, the same type of photosensitive surfaces can output one output light intensity. If the product of the photoresponse of the photosensitive surface and the amplification factor of the amplifying circuit matched with the photosensitive surface is not the same preset value, a corresponding method is needed to be adopted to enable the product to be the same preset value.

The output light intensity of the same type of photosensitive surface can be realized by adopting a hardware or software mode.

The first mode is a hardware mode. Cathodes and anodes of different photosurfaces in the same type of photosurfaces can be electrically connected with each other, namely, the common-cathode-common-anode electrical connection between different photosurfaces is realized. In this case, it is equivalent to connect different photosensitive surfaces in parallel to realize the combined use of one or more photosensitive surfaces for outputting an output light intensity. It should be noted that it is necessary to ensure the photoresponse rates of different photosensitive surfaces to be consistent as much as possible to obtain more accurate output light intensity.

Mode two, software mode. Cathodes among different photosensitive surfaces in the same type of photosensitive surfaces are not connected with each other, and anodes among the different photosensitive surfaces are not connected with each other, namely, each photosensitive surface is independently used, and a light intensity value is output. After the light intensity value corresponding to each photosensitive surface is obtained, the light intensity values of the photosensitive surfaces of the same type can be weighted and summed by adopting a corresponding algorithm to obtain an output light intensity.

Alternatively, the output light intensity corresponding to the same kind of photosensitive surface can be determined by the following equations (2) and (3).

Wherein I represents the output light intensity corresponding to the same kind of photosensitive surface, I _i Representing a light intensity value corresponding to a photosurface i, wherein i belongs to {1, 2.... Once.N-1, N }, N represents the number of photosurfaces included in the same type of photosurfaces, N is more than or equal to 1 and less than or equal to M, M represents the total number of the photosurfaces, alpha i represents a weighting coefficient corresponding to the photosurface i, H represents a preset value, and beta represents a weighting coefficient corresponding to the photosurface i _i Indicating the photoresponse, γ, corresponding to the photosurface i _i The magnification of the amplifier circuit used in conjunction with the photosensitive surface i is shown.

According to the embodiment of the disclosure, the output light intensity is a light intensity value obtained by collecting the converged emergent light by the photosensitive surface.

According to the embodiment of the disclosure, in order to realize that the emergent light emitted from each emergent position can be converged by adopting the light-sensitive surface with a smaller area to receive the emergent area with a larger area, the converging method can be used for converging the emergent light emitted from each emergent position, so that the light intensity value of the converged emergent light can be collected by the light-sensitive surface. The converging method can be realized by adopting a photosensitive surface matched with a lens. Note that the smaller area of the light-sensing surface is larger than the area of the emission region.

According to the embodiment of the disclosure, since the photosensitive surface can be designed to be smaller, the cost can be reduced, and in addition, the efficiency of receiving the emergent light by the photosensitive surface is not influenced too much.

According to the embodiment of the disclosure, each photosensitive surface collects the light intensity value of emergent light corresponding to a target wavelength, wherein the target wavelength belongs to a plurality of preset wavelengths.

According to the embodiments of the present disclosure, generally, in order to implement the detection of light with a plurality of preset wavelengths, a time division detection manner may be adopted, that is, the detection of light with one preset wavelength is implemented at the same time. In order to realize the simultaneous detection of light with a plurality of preset wavelengths, aiming at each preset wavelength, the light-sensitive surface can collect the light intensity value of emergent light corresponding to the target wavelength, and the target wavelength refers to the preset wavelength capable of being collected by the light-sensitive surface. Alternatively, a corresponding filter film may be provided on the photosensitive surface.

According to the embodiment of the disclosure, the photosensitive surface is obtained after a mask plate is arranged on the initial photosensitive surface, and the light transmittance of the mask plate is smaller than or equal to the light transmittance threshold.

According to the embodiment of the present disclosure, the shape of the mask is determined according to the dither distribution shape of the outgoing light.

According to the embodiment of the disclosure, because the current round photosensitive surface or the square photosensitive surface is common, the manufacturing process difficulty is small, the manufacturing cost is low, and the photosensitive surfaces of other shapes are generally required to be customized, the manufacturing process difficulty is large, and the manufacturing cost is high, therefore, if the manufacturing cost is limited, a mode of setting a mask plate on the initial photosensitive surface can be adopted, wherein the part of the initial photosensitive surface, which is shielded by the mask plate, is difficult to receive the light intensity value because the light transmittance of the mask plate is less than or equal to the light transmittance threshold value.

Based on the above, the shape and the position of the mask plate can be set according to the actually required shape and area, so that the photosensitive surface with the preset shape and area can be obtained. Wherein, the shape and the area which are actually needed can be determined according to the jitter distribution condition of the emergent light.

For example, fig. 10 schematically illustrates a schematic diagram of a photosensitive surface obtained by disposing a mask on an initial photosensitive surface according to an embodiment of the disclosure. In fig. 10, the initial photosensitive surface is a square photosensitive surface, and the photosensitive surface is a circular photosensitive surface.

According to the embodiment of the present disclosure, the intensity distribution of the spot irradiated by the incident light to the detection area is uniform.

According to the embodiment of the disclosure, in order to enable the detected object to perform tissue composition detection under a more relaxed requirement, thereby better ensuring the detection precision, the detection method can be realized by adopting a mode of ensuring that the intensity distribution of the light spot irradiated to the detection area by the incident light is uniform. Meanwhile, the more uniform the intensity distribution of the light spot irradiated to the detection area by the incident light is, the lower the requirement on the reproducibility of the controllable detection condition is, and the better the effect of suppressing the influence of the uncontrollable detection condition on the detection result by adopting a differential detection method is, so that the detection precision can be better ensured. In addition, since the light energy of the incident light is attenuated to some extent by the measure of making the intensity distribution of the spot of the incident light on the detection area uniform, and the light energy of the incident light required for tissue composition detection cannot be too small, it is necessary to attenuate the light energy of the incident light as small as possible while ensuring the intensity distribution of the spot of the incident light on the detection area uniform as much as possible. In addition, if the incident light is realized by adopting an optical fiber transmission mode, the light spots of the incident light are uniformly distributed on the detection area, and the adverse effect of optical fiber jitter on the detection result is also reduced.

According to the embodiment of the present disclosure, the area of the light spot irradiated to the detection region by the incident light is greater than or equal to the light spot area threshold value.

According to the embodiment of the disclosure, in order to enable the detected object to perform tissue composition detection under a more relaxed requirement, thereby better ensuring the detection accuracy, the method can be implemented in a manner that the area of the light spot irradiated to the detection area by the incident light is greater than or equal to the light spot area threshold. Meanwhile, in a certain range, the larger the area of a light spot irradiated to the detection area by incident light is, the lower the requirement on the reproducibility of the controllable detection condition is, and the better the effect of inhibiting the influence of the uncontrollable detection condition on the detection result by adopting a differential detection method is, so that the detection precision can be better ensured. The spot area threshold may be set according to actual conditions, and is not specifically limited herein. In addition, if the incident light is realized by adopting an optical fiber transmission mode, the area of a light spot irradiated to the detection area by the incident light is larger than or equal to a light spot area threshold value, and the adverse effect of optical fiber jitter on the detection result is also reduced.

FIG. 11 schematically illustrates a block diagram of an apparatus for detecting a composition of living tissue according to an embodiment of the present disclosure.

As shown in FIG. 11, an apparatus 1100 for detecting a composition of a living tissue includes a light source module 1110, an acquisition module 1120, and a processing module 1130.

The light source module 1110 is configured to irradiate a detection area with at least one incident light with a preset wavelength, where the incident light passes through the detection area and then exits from at least one exit position to form at least one bundle of exit light, and the incident positions of the incident light include at least two.

The collection module 1120 comprises M photosensitive surfaces, wherein each photosensitive surface can collect the light intensity value of emergent light emitted from the emergent position in the preset anti-shake range corresponding to the photosensitive surface, the collection module is used for acquiring the light intensity value corresponding to each beam of emergent light collected by the M photosensitive surfaces to obtain T output light intensities, and each output light intensity is obtained by processing the light intensity value of the emergent light collected by one or more photosensitive surfaces.

The processing module 1130 is configured to determine a concentration of at least one measured tissue constituent according to at least one output light intensity corresponding to at least one preset wavelength.

According to the technical scheme of this disclosed embodiment, the light intensity value of the emergent light that the emergent position that the sensitive surface can gather in the preset disturbance range of preventing that corresponds was emergent, because the sensitive surface that has above-mentioned characteristic has improved the area that can stably receive the emergent light in the sensitive surface and has accounted for the proportion of the area of this sensitive surface, consequently, has improved the stability of receiving the emergent light, and then has reduced the adverse effect of the intensity change of the distribution of the emergent light that leads to by the shake to detection accuracy has been improved.

According to the embodiment of the disclosure, the proportion of the transmission optical path of the emergent light received by each photosensitive surface in the target tissue layer to the total optical path is greater than or equal to a proportion threshold, wherein the total optical path is the total distance transmitted by the emergent light in the detection area.

According to the embodiment of the disclosure, the total area of the same type of photosensitive surfaces is determined according to the tissue structure characteristics in the detection area, wherein the same type of photosensitive surfaces comprises one or more photosensitive surfaces, and the same type of photosensitive surfaces are used for outputting an output light intensity.

According to the embodiment of the disclosure, the included angle between each part of the photosensitive surface and the direction of the corresponding incident light is greater than or equal to 0 degree and less than or equal to 360 degrees.

According to the embodiment of the disclosure, the included angle between each part of the photosensitive surface and the direction of the corresponding incident light is greater than or equal to 0 degree and less than or equal to 360 degrees, so as to realize diffusion detection. According to the embodiment of the disclosure, the setting position of the suitable photosensitive surface can be determined according to the wavelength characteristic and/or the detection area characteristic, wherein the wavelength characteristic can comprise the penetration depth of the wavelength, and the detection area characteristic can comprise the thickness of the detection area. Alternatively, the angles between the portions of the photosensitive surface and the corresponding incident light direction may be set to be a predetermined angle.

For example, if the penetration depth of the wavelength is deep and/or the thickness of the detection region is thin, the position of the light sensing surface and the corresponding incident position of the incident light may be located on the opposite side of the detection region. If the penetration depth of the wavelength is shallow and/or the thickness of the detection area is thick, the position of the photosensitive surface and the corresponding incident position of the incident light can be set to be on the same side of the detection area.

Illustratively, FIG. 12 schematically illustrates a schematic diagram of diffuse detection according to an embodiment of the present disclosure. In fig. 12, the included angle between the light sensing surface C and the incident light is 90 °, the position of the light sensing surface D and the position of the incident light are located on the same side of the detection area, and the position of the light sensing surface E and the position of the incident light are located on the different side of the detection area.

According to the embodiment of the disclosure, one or more same-type photosensitive surfaces corresponding to each preset wavelength exist in the M photosensitive surfaces, wherein the same-type photosensitive surfaces are used for collecting first output light intensity and/or second output light intensity corresponding to the preset wavelengths at different moments, the first output light intensity is systolic light intensity, the second output light intensity is diastolic light intensity, and the same-type photosensitive surfaces comprise one or more photosensitive surfaces. The processing module 1130 is configured to determine a concentration of at least one measured tissue component according to the first output light intensity and the second output light intensity corresponding to each preset wavelength.

According to the embodiment of the disclosure, a first similar photosensitive surface and a second similar photosensitive surface corresponding to each preset wavelength exist in the M photosensitive surfaces, wherein the first similar photosensitive surface is used for collecting first output light intensity corresponding to the preset wavelength, the second similar photosensitive surface is used for collecting second output light intensity corresponding to the preset wavelength, the first similar photosensitive surface comprises one or more photosensitive surfaces, and the second similar photosensitive surface comprises one or more photosensitive surfaces. The processing module 1130 is configured to determine a concentration of at least one measured tissue component according to the first output light intensity and the second output light intensity corresponding to each preset wavelength.

According to the embodiment of the disclosure, the M photosurfaces have the same type photosurfaces corresponding to each preset wavelength, wherein the same type photosurfaces are used for acquiring the third output light intensity corresponding to the preset wavelength, and the same type photosurfaces comprise one or more photosurfaces. The processing module 1130 is configured to perform differential processing on the third output light intensities corresponding to different preset wavelengths to obtain at least one differential signal, and determine the concentration of the detected tissue component according to the at least one differential signal.

According to an embodiment of the present disclosure, the processing module 1130 is configured to perform difference processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a difference signal, perform direct difference operation on the difference signal corresponding to different preset wavelengths to obtain at least one wavelength difference signal, and determine the concentration of the measured tissue component according to the at least one wavelength difference signal.

According to the embodiment of the disclosure, the M photosurfaces have the same type photosurfaces corresponding to each preset wavelength, wherein the same type photosurfaces are used for acquiring the fourth output light intensity corresponding to the preset wavelength, and the same type photosurfaces comprise one or more photosurfaces. And a processing module 1130, configured to determine a concentration of at least one measured tissue component according to the fourth output light intensities corresponding to the respective preset wavelengths.

According to the embodiment of the disclosure, the difference value between the average optical path of the emergent light received by different photosensitive positions of each photosensitive surface in the same type of photosensitive surface and the optimal optical path corresponding to the preset wavelength belongs to the second optical path difference range.

According to this disclosed embodiment, the photosurface of the same kind is annular photosurface, includes: in the case where the similar photosensitive surface includes one photosensitive surface, the similar photosensitive surface is an independent annular photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is an annular photosensitive surface formed by combining the plurality of photosensitive surfaces. The similar photosurface is a non-annular photosurface and comprises: in the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed according to a combination of the plurality of photosensitive surfaces.

According to the embodiment of the disclosure, under the condition that the distance from the similar photosensitive surface to the target part is determined to be greater than or equal to the first distance threshold, the similar photosensitive surface comprises an annular photosensitive surface, a sector photosensitive surface, a circular photosensitive surface or a square photosensitive surface.

According to the embodiment of the disclosure, in the case that it is determined that the distance from the same type of photosensitive surface to the target portion is less than or equal to the second distance threshold, the shape of the same type of photosensitive surface is determined according to the jitter distribution of the outgoing light.

According to the embodiment of the disclosure, the similar photosensitive surface comprises a rectangular photosensitive surface or an elliptical photosensitive surface, the ratio of the length to the width of the rectangular photosensitive surface is determined according to the ratio of the jitter amplitude of the emergent light in the first direction to the jitter amplitude of the emergent light in the second direction, and the ratio of the long axis to the short axis of the elliptical photosensitive surface is determined according to the ratio of the jitter amplitude of the emergent light in the first direction to the jitter amplitude of the emergent light in the second direction.

According to the embodiment of the disclosure, the anodes of different photosensitive surfaces in the M photosensitive surfaces are not electrically connected with each other, the anodes of partial photosensitive surfaces are electrically connected, or the anodes of all photosensitive surfaces are electrically connected.

According to an embodiment of the present disclosure, each of the M photosurfaces may be used alone, in which case the anodes of different ones of the M photosurfaces are not electrically connected.

Some of the M photosurfaces may be used in combination, in which case the anodes of the different photosurfaces used in combination are electrically connected.

All of the M photosurfaces may be used in combination, in which case the anodes of the different photosurfaces used in combination are electrically connected.

Fig. 13 schematically illustrates a schematic diagram of an electrical connection of anodes of different photosurfaces according to an embodiment of the disclosure. As shown in fig. 13, the anodes of all the photosensitive surfaces are electrically connected.

According to embodiments of the present disclosure, different portions of the same photosurface are in the same plane or different planes.

According to the embodiments of the present disclosure, the photosensitive surface may be a planar photosensitive surface or a stereoscopic photosensitive surface, wherein if different portions of the photosensitive surface are all in the same plane, the photosensitive surface is a planar photosensitive surface. If different parts of the light-sensitive surface are on different planes, the light-sensitive surface is a three-dimensional light-sensitive surface. Specifically, the planar photosensitive surface or the three-dimensional photosensitive surface may be set according to actual conditions, and is not particularly limited herein.

Alternatively, for contact detection, in order to improve detection accuracy, it is necessary to make the target surface of the photosensitive surface and the skin surface of the detection area in a better fit state as much as possible. Wherein the target surface of the photosurface represents a surface that is proximate to the detection region. Because the flatness of the skin surface of the detection area may not be high, if a planar photosensitive surface is adopted, it may be difficult to achieve a good fit state between the target surface of the photosensitive surface and the skin surface of the detection area, and the stereoscopic photosensitive surface is a photosensitive surface having different portions in different planes, so that a stereoscopic photosensitive surface may be adopted, and a form of a specific stereoscopic photosensitive surface may be set according to the tissue structure characteristics of the detection area.

Fig. 14 schematically illustrates a schematic view of a medium gloss in the form of a glove according to an embodiment of the present disclosure. FIG. 15 schematically illustrates a schematic view of another glove-form stereoscopic light in accordance with an embodiment of the present disclosure.

Fig. 16 schematically illustrates a schematic view of a stereoscopic photosurface in the form of a bracelet according to an embodiment of the disclosure. Fig. 17 schematically illustrates a schematic view of a stereoscopic photosurface in another bracelet form according to an embodiment of the disclosure.

Fig. 18 schematically illustrates a schematic view of a stereoscopic optical surface for arm detection according to an embodiment of the present disclosure. In fig. 18, the distances of different portions of the photosurface from the predetermined plane can be set according to the anatomical features of the arm. H in FIG. 18 ₁ And h ₂ Indicating the distance of different portions of the photosurface from the predetermined plane.

According to the embodiment of the disclosure, the photosensitive surfaces are collected on the same plane or different planes, wherein the photosensitive surface collection comprises a plurality of photosensitive surfaces.

According to an embodiment of the present disclosure, each photosurface included in the set of photosurfaces may be a planar photosurface or a stereoscopic photosurface. If the photosensitive surface set comprises a plurality of plane photosensitive surfaces, a mode that part of the plane photosensitive surfaces or all the plane photosensitive surfaces in the plurality of plane photosensitive surfaces are arranged on different planes can be adopted to realize that the photosensitive surface form presented by the photosensitive surface set is a stereoscopic photosensitive surface.

It should be noted that, according to the stereoscopic light surface formed by the plurality of planar light-sensing surfaces, the effect for the contact detection may also be achieved, and details are not described here.

According to an embodiment of the present disclosure, the apparatus 1100 for detecting living tissue components further includes a converging module disposed between the detection region and the photosensitive surface. And the converging module is used for converging the emergent light so as to realize that the output light intensity is a light intensity value acquired by the photosensitive surface after the emergent light is converged.

According to the embodiment of the disclosure, in order to realize that the light-sensitive surface with a smaller area can receive the emergent area with a larger area, the emergent light can be collected by the collecting module through the mode of arranging the collecting module between the detection area and the light-sensitive surface, namely, the emergent light emitted from different emergent positions after the incident light passes through the detection area is collected by the collecting module through the collecting module to form the emergent light after being collected, and the light intensity value of the emergent light after being collected can be collected by the light-sensitive surface.

According to an embodiment of the present disclosure, the apparatus 1100 for detecting a composition of a living tissue further includes a support module and a detection probe, the detection probe includes M photosensitive surfaces, the support module is disposed on a target surface of the photosensitive surfaces or a target surface of the detection probe, wherein the target surface of the photosensitive surfaces and the target surface of the detection probe both represent surfaces close to a detection region. And the supporting module is used for supporting the convergence module.

According to the embodiment of the disclosure, the convergence module is arranged on the support module to realize the fixation of the convergence module.

According to an embodiment of the present disclosure, the convergence module includes a convex lens or an annular lens, wherein the annular lens includes a single annular lens or is arranged by a plurality of convex lenses.

According to an embodiment of the present disclosure, the converging module may include a convex lens, and a manner of combining the convex lens and the photosensitive surface may be adopted to realize that the photosensitive surface with a smaller effective area receives a light intensity value of emergent light of an emergent area with a larger area, and referring to fig. 19, fig. 19 schematically illustrates a schematic diagram of realizing light reception by combining the convex lens and the circular photosensitive surface according to an embodiment of the present disclosure.

The converging module may include a ring lens, the ring lens may include a single ring lens, and the combination of the single ring lens and the photosensitive surface may be used to realize that the photosensitive surface with a smaller effective area receives the light intensity value of the emergent light from the emergent area with a larger area, as shown in fig. 20, fig. 20 schematically illustrates a schematic diagram of the combination of the ring lens and the ring photosensitive surface to realize light reception according to an embodiment of the present disclosure.

The converging module may include an annular lens, which may be an annular lens formed by arranging a plurality of convex lenses, as can be seen in fig. 21 to 22. Fig. 21 schematically illustrates a schematic diagram of a plurality of convex lenses arranged to form a ring lens and a ring-shaped photosensitive surface to realize light receiving in combination according to an embodiment of the disclosure. Fig. 22 schematically illustrates a schematic diagram of a plurality of convex lenses arranged to form a ring lens and a circular photosensitive surface to achieve light receiving according to an embodiment of the disclosure. The annular lens can realize the light-sensitive surface with a general shape, such as a circular light-sensitive surface or a square light-sensitive surface, and realize the light receiving of the annular emergent area.

According to the embodiment of the disclosure, the surfaces of S photosensitive surfaces in M photosensitive surfaces are respectively provided with the light filtering films, wherein M is more than or equal to 2, and M is more than or equal to S. And the filter coating is used for enabling the photosensitive surface to collect the light intensity value of emergent light corresponding to the target wavelength, wherein the target wavelength belongs to a plurality of preset wavelengths.

According to the embodiment of the disclosure, the surfaces of S photosurfaces of the M photosurfaces are respectively provided with a filter film for filtering incident light except for corresponding target wavelengths, wherein the target wavelengths represent preset wavelengths which can pass through the filter films. The number of target wavelengths may include one or more. The photosensitive surface on which the filter is disposed may be referred to as a target photosensitive surface, and the number of predetermined wavelengths that different target photosensitive surfaces can pass through may be the same or different.

Illustratively, the number of predetermined wavelengths includes 5, each of λ ₁ 、λ ₂ 、λ ₃ 、λ ₄ And λ ₅ . M = S =4, which are a photosensitive surface 1, a photosensitive surface 2, a photosensitive surface 3, and a photosensitive surface 4, respectively. Wherein the light filter film arranged on the light-sensitive surface 1 is used for passing through lambda ₁ And λ ₃ By filtering out λ ₂ 、λ ₄ And λ ₅ . For photosurface 1, the target wavelengths may include λ 1 and λ ₃ 。

The light filter film arranged on the light-sensitive surface 2 is used for passing through lambda ₂ Filtering out λ ₁ 、λ ₃ 、λ ₄ And λ ₅ . For the photosurface 2, the target wavelength may include λ ₂ 。

The light filter film arranged on the light-sensitive surface 3 is used for passing through lambda ₄ Filtering out λ ₁ 、λ ₂ 、λ ₃ And λ ₅ . For photosurface 3, the target wavelength may include λ ₄ 。

The light filter film arranged on the light-sensitive surface 4 is used for passing through lambda ₅ Filtering out λ ₁ 、λ ₂ 、λ ₃ And λ ₄ . For the photosurface 4, the target wavelength may include λ 5.

The following description will be made with reference to fig. 23 to 24. Fig. 23 schematically illustrates a schematic diagram of a ring-shaped photosensitive surface and a filter film combined to achieve light receiving according to an embodiment of the disclosure. Fig. 24 schematically illustrates a fan-ring photosensitive surface and a filter film combined to achieve light receiving according to an embodiment of the disclosure.

According to an embodiment of the present disclosure, the apparatus 1100 for detecting living tissue components further includes a mask disposed on the initial photosensitive surface, wherein a light transmittance of the mask is less than or equal to a light transmittance threshold. And the mask plate is used for setting the mask plate on the initial photosensitive surface to obtain a photosensitive surface.

According to the embodiment of the present disclosure, the shape of the mask is determined according to the shape of the jitter distribution of the outgoing light.

As shown in fig. 25, the apparatus 1100 for detecting living tissue components according to the embodiment of the present disclosure further includes a detection probe including M photosensitive surfaces, and a first sleeve 1140 is disposed on the detection probe. The first end face of the first sleeve 1140 extends beyond a target surface of the inspection probe, where the first end face represents an end face proximate to the inspection area and the target surface of the inspection probe represents a surface proximate to the inspection area.

According to an embodiment of the present disclosure, in order to shield the interference light, the first sleeve 1140 may be disposed on the detection probe such that an end surface of the first sleeve 1140, which is close to the detection region, exceeds a target surface of the detection probe. The disturbing light may comprise surface reflected light and/or diffracted light.

According to an embodiment of the present disclosure, the second end surface and/or the inner region of the first sleeve 1140 is provided with a scatterer, wherein the first end surface and the second end surface are two opposite end surfaces, and the inner region includes an inner partial region or an inner full region.

According to the embodiments of the present disclosure, in order to make the intensity distribution of the light spot irradiated to the detection area by the incident light uniform, a manner of providing a scattering object at a corresponding portion of the first sleeve may be adopted. The scatterer may comprise parchment, silica gel, or a target mixture, wherein the target mixture may comprise a mixture of polydimethylsiloxane and titanium dioxide particles.

As shown in fig. 26, the apparatus 1100 for detecting a living tissue component according to an embodiment of the present disclosure further includes a second sleeve 1150, and the second sleeve 1150 is disposed outside a target region of the first sleeve 1140, wherein the target region represents a partial region or a whole region of the first sleeve 1140 beyond a target surface of the detection probe.

According to an embodiment of the present disclosure, in order to make a spot of incident light irradiated to the detection region as large as possible, a manner of providing the second sleeve 1150 outside the target region of the first sleeve 1140 may be employed.

According to an embodiment of the present disclosure, the second sleeve 1150 is provided with a scatterer.

According to an embodiment of the present disclosure, if the second sleeve 1150 is provided, in order to make the intensity distribution of the spot irradiated to the detection area uniform by the incident light, a manner of providing scatterers at corresponding portions of the second sleeve 1150 may be employed.

According to an embodiment of the present disclosure, the inner diameter of the first sleeve 1140 is greater than or equal to an inner diameter threshold.

According to an embodiment of the present disclosure, the apertures of the first end face of the first sleeve 1140 are greater than or equal to the apertures of the second end face of the first sleeve.

According to an embodiment of the present disclosure, in order to make the spot of the incident light irradiated to the detection region as large as possible, the inner diameter of the first sleeve 1140 is greater than or equal to the inner diameter threshold value, and/or the opening of the first end surface of the first sleeve 1140 is greater than or equal to the opening of the second end surface of the first sleeve, i.e., the opening of the end surface of the first sleeve close to the detection region is greater than or equal to the opening of the end surface of the first sleeve far away from the detection region.

As shown in fig. 28 to 29, according to the embodiment of the present disclosure, an index matching substance is filled between the light sensing surface and the detection region.

According to the embodiment of the disclosure, the surface of the detection area is unstable due to the jitter, and the emergent angle of the emergent light is changed, so that in order to suppress adverse effects caused by the jitter as much as possible, a refractive index matching material can be filled between the photosensitive surface and the detection area, and the stability and efficiency of the photosensitive surface for receiving the emergent light are improved.

The description will be made by taking the jitter caused by the pulse beat as an example. The pulse beat can be reflected by the state of the blood vessels. Fig. 27 schematically illustrates a diagram of a light-sensing surface receiving emergent light without filling an index matching object according to an embodiment of the disclosure. In fig. 27, a vascular state 1 indicates a vasoconstriction state, a vascular state 2 indicates a vasodilation state, a skin state 1 indicates a skin state corresponding to the vascular state 1, and a skin state 2 indicates a skin state corresponding to the vascular state 2. As can be seen from fig. 27, the jitter causes instability of the skin surface in the detection region, and the emission angle of the emitted light changes.

Fig. 28 schematically illustrates a diagram of a photosensitive surface receiving emergent light with an index matching object filled therein according to an embodiment of the disclosure.

Fig. 29 schematically illustrates another schematic diagram of a photosensitive surface receiving emergent light with an index matching object filled therein according to an embodiment of the disclosure.

As can be seen from fig. 28 and 29, the refractive index matching material is filled between the photosensitive surface and the detection area, so that the stability and efficiency of receiving the emergent light by the photosensitive surface can be improved.

According to an embodiment of the present disclosure, the shape of the incident light includes a point shape, a line shape, or a plane shape.

According to embodiments of the present disclosure, a facet shape may include a circle, a ring, a square, a triangle, or the like.

According to an embodiment of the present disclosure, the positional relationship between the incident position and the M photosensitive surfaces includes one of: the positions of the M photosurfaces are located inside all the incident positions. The positions of the M photosensitive surfaces are outside the total incidence positions. The positions of the M photosensitive surfaces form a nesting position relationship with each incident position.

According to the embodiments of the present disclosure, the positional relationship between the incident position and the M photosensitive surfaces may include one of the following cases and will be described with reference to the drawings.

In one embodiment, the M photosurfaces are all disposed around the outside of all incident positions. The above-mentioned arrangement mode of position relation will form the implementation mode of incident of middle incident light and receiving of peripheral light. See fig. 30-32. Fig. 30 shows a case where a plurality of incident positions are incident and one photosensitive surface receives light. Fig. 31 to 32 show the case where the light enters from a plurality of entrance positions and is received by a plurality of light receiving surfaces.

Fig. 30 schematically illustrates a schematic diagram of the peripheral reception of a circular incident light and a ring-shaped incident light incident ring-shaped photosurface according to an embodiment of the disclosure.

Fig. 31 schematically illustrates a schematic diagram of a circular incident light and a ring-shaped incident light incident on the periphery of a first set of photosurfaces, the first set of photosurfaces comprising two ring-shaped photosurfaces, according to an embodiment of the disclosure. Fig. 32 schematically illustrates a schematic diagram of peripheral reception of a circular incident light and a ring-shaped incident light incident on a second set of photosurfaces, which includes four fan-ring photosurfaces, in accordance with an embodiment of the disclosure.

Second, all the incident positions are disposed around the outer portions of the M photosensitive surfaces, that is, the M photosensitive surfaces are surrounded by all the incident positions. The above-mentioned arrangement of the position relationship will form the implementation of peripheral light incidence and intermediate light reception. See fig. 33-34. Fig. 33 shows a case where a plurality of incident positions are incident and one photosensitive surface receives light. Fig. 34 shows a case where a plurality of incident positions are incident and a plurality of photosensitive surfaces are received.

Fig. 33 schematically illustrates a schematic diagram of peripheral incidence of two annular incident lights into the interior of a circular photosurface for reception according to an embodiment of the disclosure.

Fig. 34 schematically illustrates a schematic diagram of peripheral incidence of two annular incident light rays into a third set of photosurfaces and internal reception of the third set of photosurfaces, the third set comprising two annular photosurfaces, according to an embodiment of the disclosure.

And thirdly, W photosensitive surfaces in the M photosensitive surfaces are arranged around the outer part of the partial incidence position, M-W photosensitive surfaces in the M photosensitive surfaces are arranged inside the other part of the incidence position, namely the W photosensitive surfaces are arranged around the outer part of the partial incidence position, and the M-W photosensitive surfaces are surrounded by the other part of the incidence position. The above-mentioned positional relationship setting manner will form a nested reception implementation manner. See fig. 35-37. Fig. 35 shows a case where a plurality of incident positions are incident and one photosensitive surface receives light. Fig. 36 to 37 show the case where the light enters from a plurality of entrance positions and is received by a plurality of light receiving surfaces.

FIG. 35 schematically illustrates a schematic diagram of nested reception according to an embodiment of the disclosure. In fig. 35, an annular photosensitive surface is provided between an annular incident light and a circular incident light.

FIG. 36 schematically illustrates a schematic diagram of another nested reception according to an embodiment of the disclosure. FIG. 37 schematically illustrates a schematic diagram of yet another nested reception according to an embodiment of the present disclosure.

According to an embodiment of the present disclosure, the apparatus 1100 for detecting a living tissue component further includes a protection portion. And a protection part arranged on the target surface of the light sensing surface and used for protecting the light sensing surface, wherein the target surface of the light sensing surface represents a surface close to the detection area.

According to an embodiment of the present disclosure, in order to protect the light sensing surface, a protection portion may be further provided on a target surface of the light sensing surface. The material of which the guard is made may be a transparent and flexible material. The protective part may include an antireflection film or optical glass. The distance between the protective portion and the target surface of the photosensitive surface may be determined according to the material of the protective portion.

For example, if the antireflection film is disposed at the protective portion, the distance between the antireflection film and the target surface of the photosensitive surface may be zero. In another example, the protective portion is an optical glass, and a distance between the optical glass and the target surface of the light-sensing surface is greater than or equal to a distance threshold. The distance threshold value can be set according to actual conditions.

Any of the modules, units, or at least part of the functionality of any of them according to embodiments of the present disclosure may be implemented in one module. Any one or more of the modules and units according to the embodiments of the present disclosure may be implemented by being split into a plurality of modules. Any one or more of the modules, units according to the embodiments of the present disclosure may be implemented at least partially as a hardware Circuit, such as a Field Programmable Gate Array (FPGA), a Programmable Logic Array (PLA), a system on a chip, a system on a substrate, a system on a package, an Application Specific Integrated Circuit (ASIC), or any other reasonable manner of integrating or packaging a Circuit, or as any one of three implementations of software, hardware, and firmware, or as a suitable combination of any several of them. Alternatively, one or more of the modules, units according to embodiments of the present disclosure may be implemented at least partly as computer program modules, which, when executed, may perform the respective functions.

For example, any number of the acquisition modules and the processing modules may be combined and implemented in one module/unit, or any one of the modules/units may be split into a plurality of modules/units. Alternatively, at least part of the functionality of one or more of these modules/units may be combined with at least part of the functionality of other modules/units and implemented in one module/unit. According to an embodiment of the present disclosure, at least one of the acquisition module and the processing module may be implemented at least partially as a hardware circuit, such as a Field Programmable Gate Array (FPGA), a Programmable Logic Array (PLA), a system on a chip, a system on a substrate, a system on a package, an Application Specific Integrated Circuit (ASIC), or may be implemented in hardware or firmware in any other reasonable manner of integrating or packaging a circuit, or in any one of three implementations of software, hardware, and firmware, or in a suitable combination of any of them. Alternatively, at least one of the acquisition module and the processing module may be at least partly implemented as a computer program module, which when executed may perform a corresponding function.

It should be noted that the apparatus for detecting a living tissue component in the embodiment of the present disclosure corresponds to the method for detecting a living tissue component in the embodiment of the present disclosure, and the description of the apparatus for detecting a living tissue component refers to the method for detecting a living tissue component, and will not be described herein.

Fig. 38 schematically illustrates a schematic diagram of a wearable device according to an embodiment of the present disclosure. The wearable device 3800 shown in fig. 38 is merely one example, and should not bring about any limitation to the function and use range of the embodiment of the present disclosure.

As shown in fig. 38, a wearable device 3800 includes an apparatus 1100 for detecting a living tissue component.

As shown in fig. 39, the wearable device 3800 further includes a clasp portion 3810 and a body 3820, according to embodiments of the present disclosure. The clasp portion 3810 and the body 3820 are used to cooperate to implement the apparatus 1100 for fixedly detecting the composition of the living tissue.

Fig. 39 schematically shows a schematic diagram of an assembly process of a wearable device according to an embodiment of the present disclosure.

According to embodiments of the present disclosure, the mass of the wearable device 3900 is less than or equal to a mass threshold to enable the movement law of the wearable device 3900 to remain consistent with the skin-shaking law at the detection area.

According to the embodiment of the disclosure, in order to improve the detection accuracy, the quality of the wearable device 3900 can be lighter, so that when the wearable device 3900 is worn to a position corresponding to a detection area, skin shaking at the detection area can be followed, that is, the movement rule of the wearable device 3900 can be kept consistent with the skin shaking rule at the detection area, and therefore, the average optical path of emergent light received by the detection probe is kept within a preset optical path range in the skin shaking process. The reason that the above-described average optical path of the outgoing light received by the detection probe can be kept within the preset optical path range during the skin shaking process at the detection area is that if the wearable device 3900 is capable of following the skin shaking process at the detection area, it can be achieved that the relative position of the detection probe on the detection area is kept unchanged or substantially unchanged, and thus the detection probe can receive the outgoing light emitted from a fixed emission position, which means an emission position where the relative position with the detection area is kept unchanged or substantially unchanged. Meanwhile, in the process of skin shaking at the detection area, the relative position of the incident light on the detection area can be kept unchanged or basically unchanged, so that the average optical path of the emergent light can be kept unchanged as far as possible under the condition that the incident position of the incident light and the emergent position of the emergent light are determined.

For example, fig. 40 schematically shows a schematic diagram of keeping the average optical path of the outgoing light received by the detection probe within the preset optical path range during the skin-shaking process under the condition that the wearable device is consistent with the skin-shaking rule according to the embodiment of the disclosure. During the skin shaking, the detection probe (not shown in fig. 40) can stably receive the outgoing light that is emitted from the outgoing position B at the detection region after the incident light is incident from the incident position a at the detection region. Zeta for moving amplitude of skin ₁ ζ is used to indicate the moving width of the detection probe ₂ Is represented by ζ ₁ ＝ζ ₂ 。

According to embodiments of the present disclosure, the wearable device 3900 causes the amplitude of movement of the skin at the detection area to be less than or equal to the amplitude of movement threshold.

According to the embodiment of the disclosure, in order to improve the detection accuracy, the mass of the wearable device 3900 can be made larger, and when the wearable device 3900 is arranged at a position corresponding to the detection area, skin shaking at the detection area can be suppressed, that is, the moving amplitude of the skin at the detection area is less than or equal to the moving amplitude threshold value, so that the average optical path of the emergent light received by the detection probe is kept within the preset optical path range during the skin shaking. The reason why the average optical path of the emergent light received by the detection probe is kept within the preset optical path range in the skin shaking process at the detection area is that if the wearable device 3900 can press the skin shaking process at the detection area, the relative position of the detection probe on the detection area can be kept unchanged or basically unchanged as much as possible, and therefore the detection probe can receive the emergent light emitted from the fixed emission position. Meanwhile, in the process of skin shaking at the detection area, the relative position of the incident light on the detection area can be kept unchanged or basically unchanged, so that the average optical path of the emergent light can be kept unchanged as far as possible under the condition that the incident position of the incident light and the emergent position of the emergent light are determined.

For example, fig. 41 schematically shows a schematic diagram of an average optical path of outgoing light received by a detection probe in a case where a wearable device makes a movement amplitude of skin at a detection area smaller than or equal to a movement amplitude threshold value, which is kept within a preset optical path range during skin shaking according to an embodiment of the present disclosure. The amplitude of the movement of the skin at the detection region in fig. 41 is close to zero.

According to the embodiments of the present disclosure, the detailed description of the apparatus for detecting the composition of the living tissue can be referred to the above corresponding parts, and will not be described in detail herein. Further, the apparatus for detecting a living tissue component includes a processor which can perform various appropriate actions and processes in accordance with a program stored in a Read-Only Memory (ROM) or a program loaded from a storage section into a Random Access Memory (RAM). The processor may comprise, for example, a general purpose microprocessor (e.g., a CPU), an instruction set processor and/or associated chipset, and/or a special purpose microprocessor (e.g., an Application Specific Integrated Circuit (ASIC)), among others. The processing may also include onboard memory for caching purposes. The processor may comprise a single processing unit or a plurality of processing units for performing the different actions of the method flows according to embodiments of the present disclosure.

In the RAM, various programs and data necessary for the operation of the apparatus for detecting a living tissue component are stored. The processor, the ROM, and the RAM are connected to each other through a bus. The processor performs various operations of the method flows according to the embodiments of the present disclosure by executing programs in the ROM and/or RAM. Note that the program may also be stored in one or more memories other than the ROM and RAM. The processes may also perform various operations of method flows according to embodiments of the present disclosure by executing programs stored in the one or more memories.

According to embodiments of the present disclosure, the wearable device may further include an input/output (I/O) interface also connected to the bus. The wearable device may further comprise one or more of the following components connected to the I/O interface: an input section including a keyboard, a mouse, and the like; an output section including a Cathode Ray Tube (CRT), a Liquid Crystal Display (LCD), and the like, and a speaker and the like; a storage section including a hard disk and the like; and a communication section including a network interface card such as a LAN card, a modem, or the like. The communication section performs communication processing via a network such as the internet. The drive is also connected to the I/O interface as needed. A removable medium such as a magnetic disk, an optical disk, a magneto-optical disk, a semiconductor memory, or the like is mounted on the drive as needed, so that the computer program read out therefrom is mounted into the storage section as needed.

The present disclosure also provides a computer-readable storage medium, which may be contained in the apparatus/device/system described in the above embodiments; or may exist separately and not be assembled into the device/apparatus/system. The computer-readable storage medium carries one or more programs which, when executed, implement the method according to an embodiment of the disclosure.

According to an embodiment of the present disclosure, the computer-readable storage medium may be a non-volatile computer-readable storage medium. Examples may include, but are not limited to: a portable Computer diskette, a hard disk, a Random Access Memory (RAM), a Read-Only Memory (ROM), an Erasable Programmable Read-Only Memory (EPROM) or flash Memory), a portable compact Disc Read-Only Memory (CD-ROM), an optical storage device, a magnetic storage device, or any suitable combination of the preceding. In the present disclosure, a computer readable storage medium may be any tangible medium that can contain, or store a program for use by or in connection with an instruction execution system, apparatus, or device.

For example, according to embodiments of the present disclosure, a computer-readable storage medium may include the ROM and/or RAM and/or one or more memories other than ROM and RAM described above.

Embodiments of the present disclosure also include a computer program product comprising a computer program containing program code for performing the methods provided by embodiments of the present disclosure.

The computer program, when executed by a processor, performs the above-described functions defined in the system/apparatus of the embodiments of the present disclosure. The systems, apparatuses, modules, units, etc. described above may be implemented by computer program modules according to embodiments of the present disclosure.

In one embodiment, the computer program may be hosted on a tangible storage medium such as an optical storage device, a magnetic storage device, or the like. In another embodiment, the computer program may also be transmitted in the form of a signal over a network medium, distributed, and downloaded and installed via the communication section, and/or installed from a removable medium. The computer program containing program code may be transmitted using any suitable network medium, including but not limited to: wireless, wired, etc., or any suitable combination of the foregoing.

In accordance with embodiments of the present disclosure, program code for executing computer programs provided by embodiments of the present disclosure may be written in any combination of one or more programming languages, and in particular, these computer programs may be implemented using high level procedural and/or object oriented programming languages, and/or assembly/machine languages. The programming language includes, but is not limited to, programming languages such as Java, C + +, python, the "C" language, or the like. The program code may execute entirely on the user computing device, partly on the user device, partly on a remote computing device, or entirely on the remote computing device or server. In situations involving remote computing devices, the remote computing devices may be connected to the user computing device through any kind of Network, including a Local Area Network (LAN) or Wide Area Network (WAN), or may be connected to external computing devices (e.g., through the internet using an internet service provider).

The flowchart and block diagrams in the figures illustrate the architecture, functionality, and operation of possible implementations of systems, methods and computer program products according to various embodiments of the present disclosure. In this regard, each block in the flowchart or block diagrams may represent a module, segment, or portion of code, which comprises one or more executable instructions for implementing the specified logical function(s). It should also be noted that, in some alternative implementations, the functions noted in the block may occur out of the order noted in the figures. For example, two blocks shown in succession may, in fact, be executed substantially concurrently, or the blocks may sometimes be executed in the reverse order, depending upon the functionality involved. It will also be noted that each block of the block diagrams or flowchart illustration, and combinations of blocks in the block diagrams or flowchart illustration, can be implemented by special purpose hardware-based systems that perform the specified functions or acts, or combinations of special purpose hardware and computer instructions. Those skilled in the art will appreciate that various combinations and/or combinations of features recited in the various embodiments and/or claims of the present disclosure can be made, even if such combinations or combinations are not expressly recited in the present disclosure. In particular, various combinations and/or combinations of the features recited in the various embodiments and/or claims of the present disclosure may be made without departing from the spirit or teaching of the present disclosure. All such combinations and/or associations are within the scope of the present disclosure.

The embodiments of the present disclosure have been described above. However, these examples are for illustrative purposes only and are not intended to limit the scope of the present disclosure. Although the embodiments are described separately above, this does not mean that the measures in the embodiments cannot be used in advantageous combination. The scope of the disclosure is defined by the appended claims and equivalents thereof. Various alternatives and modifications can be devised by those skilled in the art without departing from the scope of the present disclosure, and such alternatives and modifications are intended to be within the scope of the present disclosure.

Claims

1. A method of detecting a composition of living tissue, comprising:

irradiating a detection area with at least one incident light with a preset wavelength, wherein the incident light passes through the detection area and then is emitted from at least one emitting position to form at least one beam of emitting light, and the incident positions of the incident light comprise at least two;

acquiring light intensity values which are acquired by M photosensitive surfaces and correspond to each emergent light beam to acquire T output light intensities, wherein each output light intensity is acquired by processing according to the light intensity value of the emergent light acquired by one or more photosensitive surfaces, each photosensitive surface can acquire the light intensity value of the emergent light emitted from an emergent position in a preset anti-shaking range corresponding to the photosensitive surface, and T is more than or equal to 1 and less than or equal to M; and

determining the concentration of at least one measured tissue constituent according to at least one output light intensity corresponding to the at least one preset wavelength;

every the photosurface can gather with the light intensity value of the emergent light that the emergent position that the presupposition that the photosurface corresponds prevented shaking within range was emergent includes:

the ratio of the area of each photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to a ratio threshold value, so that the ratio of the area corresponding to the non-edge part of the photosensitive surface to the area of the photosensitive surface is as large as possible, and the adverse effect of jitter on a detection result is effectively inhibited, wherein the perimeter represents the edge part of the photosensitive surface, and the area represents the non-edge part of the photosensitive surface.

2. The method according to claim 1, wherein the ratio of the average optical path of the emergent light received by each photosensitive surface in the target tissue layer to the total optical path is greater than or equal to a ratio threshold value, wherein the total optical path is the total distance of the emergent light transmitted in the detection area.

3. The method of claim 1 or 2, further comprising:

and determining the total area of the same type of photosensitive surfaces according to the tissue structure characteristics in the detection area, wherein the same type of photosensitive surfaces comprise one or more photosensitive surfaces, and the same type of photosensitive surfaces are used for outputting one output light intensity.

4. The method of claim 1, wherein the ratio threshold is greater than or equal to 0.04mm.

5. A method according to claim 1 or 2, wherein the photosurface is in contact with or not in contact with a surface of the detection area.

6. The method of claim 5, wherein the photosurface is at a distance from the surface of the detection region less than or equal to a first distance threshold and the efficiency at which the photosurface receives the emerging light is greater than or equal to an efficiency threshold.

7. The method of claim 1 or 2, wherein said determining the concentration of at least one measured tissue constituent from at least one output light intensity corresponding to said at least one preset wavelength comprises:

under the condition of aiming at each measured tissue component in the at least one measured tissue component, aiming at each preset wavelength in the at least one preset wavelength, determining a first output light intensity and a second output light intensity from at least two output light intensities corresponding to the preset wavelength; and

and determining the concentration of the detected tissue component according to the first output light intensity and the second output light intensity corresponding to each preset wavelength.

8. The method of claim 7, wherein said determining the concentration of the measured tissue constituent from the first and second output intensities corresponding to the respective predetermined wavelengths comprises:

carrying out differential processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal; and

and determining the concentration of the detected tissue component according to the differential signal corresponding to each preset wavelength.

9. The method of claim 8, wherein the differentiating the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal comprises:

and processing the first output light intensity and the second output light intensity corresponding to the preset wavelength by adopting a differential circuit to obtain the differential signal.

10. The method of claim 8, wherein the differentiating the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal comprises:

and processing the first output light intensity and the second output light intensity corresponding to the preset wavelength by adopting a differential algorithm to obtain the differential signal.

11. The method of claim 10, wherein the processing the first output light intensity and the second output light intensity corresponding to the preset wavelength by using a difference algorithm to obtain the difference signal comprises:

and carrying out direct differential operation on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain the differential signal.

12. The method of claim 10, wherein the processing of the first output light intensity and the second output light intensity corresponding to the preset wavelength by the difference algorithm to obtain the difference signal comprises:

carrying out logarithm processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain first logarithm light intensity and second logarithm light intensity; and

and carrying out direct differential operation on the first logarithmic light intensity and the second logarithmic light intensity corresponding to the preset wavelength to obtain the differential signal.

13. The method of claim 8, wherein the first output intensity and the second output intensity are collected from the same or different types of photosurfaces at different times, wherein the first output intensity is a systolic intensity and the second output intensity is a diastolic intensity, and the types of photosurfaces comprise one or more of the photosurfaces, and the types of photosurfaces are used for outputting one of the output intensities.

14. The method of claim 8, wherein a first output intensity corresponding to the predetermined wavelength is collected from a first homogeneous photosurface corresponding to the predetermined wavelength and a second output intensity corresponding to the predetermined wavelength is collected from a second homogeneous photosurface corresponding to the predetermined wavelength, wherein the first homogeneous photosurface comprises one or more photosurfaces and the second homogeneous photosurface comprises one or more photosurfaces.

15. The method of claim 14, wherein the first and second homogeneous photosurfaces are the same homogeneous photosurfaces and the emergent light received by the first and second homogeneous photosurfaces is transmitted from incident light from different incident positions.

16. The method of claim 14, wherein the first and second homogeneous photosurfaces are different homogeneous photosurfaces.

17. The method of claim 14, wherein the average optical path length of the outgoing light received at the different photosites of each photosurface of the first generic type falls within a first average optical path range, wherein the first average optical path range is determined according to a first optical path average value, and the first optical path average value is an average value calculated according to the average optical path length of the outgoing light received at each photosite of the first generic type photosurface;

the average optical path of the emergent light received by different photosensitive positions of each photosensitive surface in the second similar photosensitive surface belongs to a second average optical path range, wherein the second average optical path range is determined according to a second optical path average value, and the second optical path average value is an average value obtained by calculating the average optical path of the emergent light received by each photosensitive position of the second similar photosensitive surface.

18. The method of claim 17, wherein an absolute value of a difference of the first path length average and the second path length average belongs to a first path length difference range.

19. The method of claim 18, wherein the first average optical path range is less than or equal to the first optical path difference range and the second average optical path range is less than or equal to the first optical path difference range.

20. The method of claim 18, wherein the first optical path difference range is determined according to an optimal differential optical path corresponding to the preset wavelength.

21. The method of claim 14, wherein a source-sensing distance of each of the photosurfaces of a first class corresponding to the predetermined wavelength from a center of the incident light is within a predetermined source-sensing distance range corresponding to the predetermined wavelength, wherein the predetermined source-sensing distance range is determined according to a source-sensing distance of a floating reference position corresponding to the predetermined wavelength from the center of the incident light.

22. The method according to claim 1 or 2, wherein said determining the concentration of at least one measured tissue component from at least one output light intensity corresponding to said at least one preset wavelength comprises:

determining, for each of the at least one preset wavelengths, a third output light intensity from at least one output light intensity corresponding to the preset wavelength, in case for each of the at least one measured tissue component;

carrying out differential processing on the third output light intensities corresponding to different preset wavelengths to obtain at least one differential signal; and

determining the concentration of the measured tissue constituent based on the at least one differential signal.

23. The method of claim 8, wherein said determining the concentration of said measured tissue constituent from the differential signal corresponding to each of said predetermined wavelengths comprises:

carrying out direct differential operation on differential signals corresponding to different preset wavelengths to obtain at least one wavelength differential signal; and

and determining the concentration of the detected tissue component according to the at least one wavelength differential signal.

24. The method of claim 1 or 2, wherein said determining the concentration of at least one measured tissue constituent from at least one output light intensity corresponding to said at least one preset wavelength comprises:

under the condition of aiming at each measured tissue component in the at least one measured tissue component, aiming at each preset wavelength in the at least one preset wavelength, determining at least one superposed light intensity corresponding to the preset wavelength, wherein the superposed light intensity is obtained by adding a plurality of output light intensities corresponding to the preset wavelength; and

and determining the concentration of the detected tissue component according to at least one superposed light intensity corresponding to each preset wavelength.

25. The method of claim 1 or 2, wherein said determining the concentration of at least one measured tissue constituent from at least one output light intensity corresponding to said at least one preset wavelength comprises:

determining, for each of the at least one preset wavelengths, a fourth output light intensity from the at least one output light intensity corresponding to the preset wavelength, in case for each of the at least one measured tissue component; and

and determining the concentration of the detected tissue component according to the fourth output light intensity corresponding to each preset wavelength.

26. The method of claim 25, wherein a fourth output intensity corresponding to the predetermined wavelength is collected from a similar photosurface corresponding to the predetermined wavelength, and a difference between an average optical path length of emergent light received by different photosurfaces of each photosurface of the similar photosurface and an optimal optical path length corresponding to the predetermined wavelength is within a second optical path difference range.

27. A method according to claim 1 or 2, wherein each said photosurface comprises an annular photosurface or a non-annular photosurface, the shape of the different photosurfaces being the same or different.

28. The method of claim 27, wherein the non-annular photosurface comprises a sector ring photosurface, a circular photosurface, a sector photosurface, an elliptical photosurface or a polygonal photosurface.

29. The method of claim 28, wherein the polygonal photosurface comprises a square photosurface, a rectangular photosurface or a triangular photosurface.

30. The method of claim 27, wherein a photosurface of the same type comprises either said annular photosurface or said non-annular photosurface, wherein said photosurface of the same type comprises one or more of said photosurfaces, said photosurfaces of the same type being configured to output one of said output intensities.

31. The method of claim 30, wherein the homogeneous photosurface is the annular photosurface and comprises:

under the condition that the same type of photosensitive surface comprises one photosensitive surface, the same type of photosensitive surface is an independent annular photosensitive surface;

under the condition that the same type of photosensitive surface comprises a plurality of photosensitive surfaces, the same type of photosensitive surface is an annular photosensitive surface formed by combining the plurality of photosensitive surfaces;

the same kind of photosensitive surface is the non-annular photosensitive surface, and comprises:

under the condition that the same type of photosensitive surface comprises one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface;

and under the condition that the same type of photosensitive surface comprises a plurality of photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed by combining the plurality of photosensitive surfaces.

32. The method of claim 31, wherein the similar photosurfaces comprise annular photosurfaces, sector-ring photosurfaces, sector-shaped photosurfaces, circular photosurfaces or square photosurfaces upon determining that the distance of the similar photosurfaces from the target site is greater than or equal to a second distance threshold.

33. The method of claim 32 wherein the shape of the homogeneous photosurface is determined from the dither distribution of the emerging light upon determining that the homogeneous photosurface is less than or equal to a third distance threshold from the target site.

34. The method of claim 33 wherein the dither distribution of the outgoing light includes a dither distribution decomposed into a dither distribution in a first direction and a dither distribution in a second direction, the first direction and the second direction being perpendicular to each other, a ratio of a length of the same kind of photosensitive surface in the first direction to a length of the same kind of photosensitive surface in the second direction being determined according to a ratio of a dither amplitude of the outgoing light in the first direction to a dither amplitude of the outgoing light in the second direction, the dither amplitude of the outgoing light in the first direction being largest.

35. The method of claim 34 wherein the photosurfaces of the same type comprise rectangular photosurfaces or elliptical photosurfaces, the ratio of length to width of the rectangular photosurfaces is determined according to the ratio of the dither amplitude of the outgoing light in the first direction to the dither amplitude of the outgoing light in the second direction, and the ratio of the major axis to the minor axis of the elliptical photosurfaces is determined according to the ratio of the dither amplitude of the outgoing light in the first direction to the dither amplitude of the outgoing light in the second direction.

36. The method according to claim 1 or 2, wherein each of the output light intensities is processed according to a light intensity value of emergent light collected by one or more photosensitive surfaces, and comprises the following steps:

combining said one or more photosurfaces to output one said output intensity; or

And under the condition that each photosensitive surface in the one or more photosensitive surfaces is used independently, calculating the light intensity value of emergent light collected by each photosensitive surface to obtain one output light intensity.

37. The method according to claim 1 or 2, wherein the output light intensity is a light intensity value collected by the photosensitive surface after the emergent light is converged.

38. The method according to claim 1 or 2, wherein each photosensitive surface collects a light intensity value of outgoing light corresponding to a target wavelength, wherein the target wavelength belongs to the at least one preset wavelength.

39. The method according to claim 1 or 2, wherein the photosensitive surface is obtained by arranging a mask on an initial photosensitive surface, and the light transmittance of the mask is less than or equal to a light transmittance threshold.

40. The method of claim 39, wherein the shape of the mask is determined according to a shape of a jitter distribution of the exiting light.

41. The method according to claim 1 or 2, wherein the intensity distribution of the spot of the incident light impinging on the detection area is uniform.

42. The method of claim 1 or 2, wherein the area of the spot of the incident light impinging on the detection region is greater than or equal to a spot area threshold.

43. An apparatus for detecting a composition of a living tissue, comprising:

the device comprises a light source module, a detection module and a control module, wherein the light source module is used for irradiating a detection area with at least one incident light with a preset wavelength, the incident light passes through the detection area and then is emitted from at least one emitting position to form at least one bundle of emitting light, and the incident positions of the incident light comprise at least two;

the collecting module comprises M photosensitive surfaces, each photosensitive surface can collect the light intensity value of emergent light emitted from an emergent position in a preset anti-shaking range corresponding to the photosensitive surface, the collecting module is used for acquiring the light intensity value corresponding to each beam of emergent light collected by the M photosensitive surfaces to obtain T output light intensities, and each output light intensity is obtained by processing the light intensity value of the emergent light collected by one or more photosensitive surfaces; and

the processing module is used for determining the concentration of at least one measured tissue component according to at least one output light intensity corresponding to at least one preset wavelength;

every the photosurface can gather with the light intensity value of the emergent light that the emergent position that predetermines in the anti-shake scope that the photosurface corresponds was emergent includes:

the ratio of the area of each photosensitive surface to the perimeter of the photosensitive surface is larger than or equal to a ratio threshold value, so that the ratio of the area corresponding to the non-edge part of the photosensitive surface to the area of the photosensitive surface is as large as possible, and the adverse effect of jitter on a detection result is effectively inhibited, wherein the perimeter represents the edge part of the photosensitive surface, and the area represents the non-edge part of the photosensitive surface.

44. The device of claim 43, wherein a ratio of a total optical path length of the emergent light received by each photosensitive surface in a target tissue layer to a total optical path length is greater than or equal to a ratio threshold, wherein the total optical path length is a total distance of the emergent light transmitted in the detection area.

45. The apparatus of claim 43 or 44, wherein a total area of homogeneous photosensitive surfaces comprising one or more of said photosensitive surfaces is determined based on tissue structure characteristics within said detection region, said homogeneous photosensitive surfaces being configured to output one of said output intensities.

46. The apparatus of claim 43, wherein the ratio threshold is greater than or equal to 0.04mm.

47. The apparatus of claim 43 or 44, wherein the photosurface is in contact with or not in contact with a surface of the detection region.

48. The apparatus of claim 47 wherein the photosurface is at a distance from the surface of the detection region less than or equal to a first distance threshold and the efficiency at which the photosurface receives outgoing light is greater than or equal to an efficiency threshold.

49. The apparatus of claim 43, wherein the angle between each portion of the photosurface and the direction of the corresponding incident light is greater than or equal to 0 ° and less than or equal to 360 °.

50. The apparatus of claim 49, wherein one or more of said M photosurfaces corresponding to each of said predetermined wavelengths are present, wherein said photosurfaces are configured to acquire a first output intensity and/or a second output intensity corresponding to said predetermined wavelengths at different times, wherein said first output intensity is a systolic intensity and said second output intensity is a diastolic intensity, and wherein said photosurfaces of the same type comprise one or more of said photosurfaces;

and the processing module is used for determining the concentration of the at least one measured tissue component according to the first output light intensity and the second output light intensity corresponding to each preset wavelength.

51. The apparatus of claim 49, wherein there are a first homogeneous photosurface and a second homogeneous photosurface corresponding to each of the preset wavelengths, wherein the first homogeneous photosurface is used for acquiring a first output light intensity corresponding to the preset wavelength, the second homogeneous photosurface is used for acquiring a second output light intensity corresponding to the preset wavelength, the first homogeneous photosurface comprises one or more photosurfaces, and the second homogeneous photosurface comprises one or more photosurfaces;

52. The apparatus of claim 51, wherein the first and second homogeneous photosurfaces are the same homogeneous photosurfaces and the emergent light received by the first and second homogeneous photosurfaces is transmitted from incident light from different incident positions.

53. The apparatus of claim 51 wherein the first and second homogeneous photosurfaces are different homogeneous photosurfaces.

54. The apparatus of claim 51 wherein the average optical path length of the emitted light received at the different photosites of each photosurface of the first class of photosurfaces falls within a first average optical path range, wherein the first average optical path range is determined according to a first optical path average value calculated from the average optical path lengths of the emitted light received at the photosites of the first class of photosurfaces;

55. The apparatus of claim 54, wherein an absolute value of a difference of the first path length average and the second path length average falls within a first path length difference range.

56. The apparatus of claim 55 wherein the first average optical path range is less than or equal to the first optical path difference range and the second average optical path range is less than or equal to the first optical path difference range.

57. The apparatus of claim 55, wherein the first optical path difference range is determined according to an optimal differential optical path corresponding to the preset wavelength.

58. The apparatus of claim 51, wherein a source-probe distance of each of the photosurfaces of a first class corresponding to the predetermined wavelength from a center of the incident light is within a predetermined source-probe distance range corresponding to the predetermined wavelength, wherein the predetermined source-probe distance range is determined according to a source-probe distance of a floating reference position corresponding to the predetermined wavelength from the center of the incident light.

59. The apparatus of claim 49, wherein there are similar photosurfaces corresponding to each of the preset wavelengths for the M photosurfaces, wherein the similar photosurfaces are used for acquiring a third output light intensity corresponding to the preset wavelengths, and the similar photosurfaces comprise one or more photosurfaces;

and the processing module is used for carrying out differential processing on the third output light intensities corresponding to different preset wavelengths to obtain at least one differential signal, and determining the concentration of the detected tissue component according to the at least one differential signal.

60. The device according to claim 50 or 51, wherein the processing module is configured to perform a difference processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a difference signal, perform a direct difference operation on the difference signals corresponding to different preset wavelengths to obtain at least one wavelength difference signal, and determine the concentration of the detected tissue component according to the at least one wavelength difference signal.

61. The apparatus of claim 49, wherein said M photosurfaces have a same type of photosurface corresponding to each of said preset wavelengths, wherein said same type of photosurface is used for acquiring a fourth output light intensity corresponding to said preset wavelengths, and said same type of photosurfaces comprises one or more of said photosurfaces;

and the processing module is used for determining the concentration of the at least one measured tissue component according to the fourth output light intensity corresponding to each preset wavelength.

62. The apparatus of claim 61, wherein the difference between the average optical path length of the emergent light received by each of the photosensitive surfaces of the same kind at different photosensitive positions and the optimal optical path length corresponding to the preset wavelength belongs to a second optical path length difference range.

63. An apparatus as claimed in claim 43 or 44, wherein each of the photosurfaces comprises an annular photosurface or a non-annular photosurface, and the shapes of the different photosurfaces are the same or different.

64. The apparatus of claim 63, wherein the non-annular photosurface comprises a sector-ring photosurface, a circular photosurface, a sector-shaped photosurface, an elliptical photosurface or a polygonal photosurface.

65. The apparatus of claim 64, wherein the polygonal photosurface comprises a square photosurface, a rectangular photosurface or a triangular photosurface.

66. The apparatus of claim 63 wherein like photosurfaces comprise either said annular photosurfaces or said non-annular photosurfaces, wherein said like photosurfaces comprise one or more of said photosurfaces and said like photosurfaces are configured to output one of said output intensities.

67. The apparatus of claim 66, wherein the homogeneous photosurface is the annular photosurface and comprises:

68. The apparatus of claim 67, wherein the similar photosurfaces comprise annular photosurfaces, sector-ring photosurfaces, sector-shaped photosurfaces, circular photosurfaces or square photosurfaces upon determining that the distance of the similar photosurfaces from the target site is greater than or equal to a second distance threshold.

69. The apparatus of claim 68 wherein the shape of the homogeneous photosurface is determined from the dither distribution of the emerging light upon determining that the homogeneous photosurface is less than or equal to a third distance threshold from the target site.

70. The apparatus of claim 69 wherein the dither distribution of the emerging light includes a dither distribution decomposed into a dither distribution in a first direction and a dither distribution in a second direction, the first direction and the second direction being perpendicular to each other, a ratio of a length of the photosurface of the same kind in the first direction to a length of the photosurface of the same kind in the second direction being determined according to a ratio of a dither amplitude of the emerging light in the first direction to a dither amplitude of the emerging light in the second direction, the dither amplitude of the emerging light in the first direction being largest.

71. The device of claim 70, wherein the photosurface of the same type comprises a rectangular photosurface or an elliptical photosurface, a ratio of a length to a width of the rectangular photosurface is determined according to a ratio of a dither amplitude of the outgoing light in the first direction to a dither amplitude of the outgoing light in the second direction, and a ratio of a long axis to a short axis of the elliptical photosurface is determined according to a ratio of a dither amplitude of the outgoing light in the first direction to a dither amplitude of the outgoing light in the second direction.

72. The apparatus of claim 43 or 44, wherein anodes of different ones of the M photosurfaces are not electrically connected to each other, anodes of some photosurfaces are electrically connected, or anodes of all photosurfaces are electrically connected.

73. A device according to claim 43 or 44, wherein different parts of the same photosurface are in the same plane or in different planes.

74. The apparatus of claim 43 or 44, wherein the set of photosurfaces is in the same plane or in different planes, wherein the set of photosurfaces comprises a plurality of photosurfaces.

75. The apparatus of claim 43 or 44, further comprising a collection module disposed between the detection region and the photosurface;

the convergence module is used for converging the emergent light so as to realize that the output light intensity is a light intensity value acquired by the photosensitive surface after the emergent light is converged.

76. The apparatus according to claim 75, further comprising a support module and a detection probe, the detection probe comprising the M photosurfaces, the support module being disposed on a target surface of the photosurfaces or a target surface of the detection probe, wherein the target surfaces of the photosurfaces and the detection probe each represent a surface proximate to the detection region;

the supporting module is used for supporting the convergence module.

77. The apparatus of claim 75, wherein the converging module comprises a convex lens or an annular lens, wherein the annular lens comprises a single annular lens or is arranged by a plurality of convex lenses in a ring.

78. The device of claim 43 or 44, wherein the surfaces of S photosensitive surfaces of the M photosensitive surfaces are respectively provided with a filter film, wherein M is greater than or equal to 2 and M is greater than or equal to S;

the filter film is used for enabling the photosensitive surface to collect a light intensity value of emergent light corresponding to a target wavelength, wherein the target wavelength belongs to the at least one preset wavelength.

79. The device according to claim 43 or 44, further comprising a mask plate, wherein the mask plate is arranged on the initial photosensitive surface, and the light transmittance of the mask plate is less than or equal to a light transmittance threshold;

the mask plate is used for setting the mask plate on the initial photosensitive surface to obtain the photosensitive surface.

80. The apparatus of claim 79, wherein the shape of the mask is determined according to a shape of a jitter distribution of the exiting light.

81. The apparatus according to claim 43 and further comprising a detection probe including the M photosurfaces, the detection probe having a first sleeve disposed thereon;

the first end face of the first sleeve extends beyond a target surface of the inspection probe, wherein the first end face represents an end face proximate to the inspection area and the target surface of the inspection probe represents a surface proximate to the inspection area.

82. The device of claim 81, wherein the first sleeve second end face and/or an inner region is provided with a diffuser, wherein the first end face and the second end face are opposite end faces, and the inner region comprises a partial region or a full region of the inner portion.

83. The apparatus according to claim 82, further comprising a second sleeve disposed outside of a target area of the first sleeve, wherein the target area represents a partial or full area of the first sleeve beyond a target surface of the detection probe.

84. The device of claim 83 wherein the second sleeve is provided with the scatterer.

85. The device of claim 82, wherein an inner diameter of the first sleeve is greater than or equal to an inner diameter threshold.

86. The device of claim 82 wherein the apertures of the first end face of the first sleeve are greater than or equal to the apertures of the second end face of the first sleeve.

87. The apparatus of claim 43 or 44, wherein an index matching substance is filled between the photosensitive surface and the detection region.

88. The device of claim 43 or 44, wherein the shape of the incident light comprises a point, line, or plane.

89. The apparatus of claim 43 or 44, wherein the positional relationship between the incident position and the M photosurfaces comprises one of:

the positions of the M photosensitive surfaces are positioned inside all the incidence positions;

the positions of the M photosensitive surfaces are positioned outside all the incidence positions;

the positions of the M photosensitive surfaces and the incidence positions form a nested position relationship.

90. The device of claim 43 or 44, further comprising a guard;

the protection part is arranged on the target surface of the light-sensing surface and used for protecting the light-sensing surface, wherein the target surface of the light-sensing surface represents a surface close to the detection area.

91. A wearable device comprising the apparatus for detecting a composition of a living tissue according to any one of claims 43 to 90.

92. The wearable device of claim 91, wherein the mass of the wearable device is less than or equal to a mass threshold to enable the wearable device movement law to stay consistent with a skin jitter law at a detection area.

93. The wearable device of claim 91, wherein the wearable device causes an amplitude of movement of skin at the detection region to be less than or equal to an amplitude of movement threshold.